Mechanisms for controlling rotation of outer cannula for use in endoscopic tool

ABSTRACT

A surgical instrument includes a cutting assembly, an outer tubing, and a flexible torque component. The cutting assembly extends from a first proximal end to a first distal end. The cutting assembly includes an outer cannula defining a cutting window and an inner cannula disposed within the outer cannula. The outer tubing extends from a proximal tubing end to a distal tubing end. The distal tubing end is coupled to the outer cannula. The outer tubing is configured to receive a torque at the proximal tubing end and transmit the torque to the outer cannula to rotate the outer cannula. The outer tubing includes a plurality of first wires and a plurality of second wires each including more than eight wires and less than twenty four wires. The flexible torque component is coupled to a third proximal end of the inner cannula to rotate the inner cannula.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application claims the benefit of and priority to U.S. Provisional Application No. 62/453,466, filed Feb. 1, 2017, titled “MECHANISMS FOR CONTROLLING ROTATION OF OUTER CANNULA FOR USE IN ENDOSCOPIC TOOL,” the entire disclosure of which is incorporated herein for any and all purposes.

BACKGROUND

Metaplasia, such as intestinal metaplasia and polyps, inside a subject, if left untreated may result in unfavorable outcomes, such as cancer. As such, physicians recommend the removal of such growths to prevent the onset of cancer and other undesirable diseases.

SUMMARY

An improved endoscopic instrument is provided that can precisely remove sessile polyps and efficiently obtain samples of multiple polyps from a patient. In particular, the improved endoscopic instrument is capable of debriding one or more polyps and retrieving the debrided polyps without having to alternate between using a separate cutting tool and a separate sample retrieving tool. The sampling can be integrated with colonoscopy inspection. In some implementations, the endoscopic instrument can cut and remove tissue from within a patient. In some such implementations, the endoscopic instrument can cut and remove tissue substantially simultaneously from within a patient accessed through a flexible endoscope.

In one aspect, a surgical instrument includes a cutting assembly, a flexible outer tubing, and a flexible torque component. The cutting assembly is configured to resect material at a site within a subject. The cutting assembly extends from a first proximal end to a first distal end. The cutting assembly includes an outer cannula and an inner cannula disposed within the outer cannula. The outer cannula defines a cutting window. The flexible outer tubing extends from a proximal tubing end to a distal tubing end. The distal tubing end is coupled to the outer cannula. The flexible outer tubing is configured to receive a torque at the proximal tubing end and transmit the torque to the outer cannula to rotate the outer cannula. The flexible outer tubing includes a plurality of first wires and a plurality of second wires each including more than eight wires and less than twenty four wires. The flexible torque component is coupled to a third proximal end of the inner cannula and configured to rotate the inner cannula relative to the outer cannula.

In another aspect, a surgical instrument includes a cutting assembly, a flexible outer tubing, and a flexible torque component. The cutting assembly extends from a first proximal end to a first distal end. The cutting assembly includes an outer cannula and an inner cannula disposed within the outer cannula. The outer cannula defines a cutting window. The flexible outer tubing extends from a proximal tubing end to a distal tubing end. The distal tubing end is coupled to the outer cannula. The flexible outer tubing is configured to receive a torque at the proximal tubing end and transmit the torque to the outer cannula to rotate the outer cannula. The flexible outer tubing includes a plurality of first wires and a plurality of second wires each including twelve wires. The flexible torque component is coupled to a third proximal end of the inner cannula and configured to rotate the inner cannula relative to the outer cannula.

In another aspect, a surgical instrument includes an end effector and a flexible outer tubing. The end effector is configured to be rotated by the flexible outer tubing to perform a surgical procedure at a site on or within a subject. The flexible outer tubing extends from a proximal tubing end to a distal tubing end. The distal tubing end is coupled to the end effector so that the flexible outer tubing can receive a torque at the proximal tubing end and transmit the torque to the end effector. The flexible outer tubing includes a plurality of first wires and a plurality of second wires oriented at an angle relative to the plurality of first wires. The plurality of first wires and plurality of second wires each include more than eight wires and less than twenty four wires.

In another aspect, an endoscopic instrument insertable within a single instrument channel of an endoscope includes a power-driven instrument head configured to resect material at a site within a subject having been reached by a flexible endoscope with working channel. The power-driven instrument head has a first distal end and a first proximal end. The first distal end of the power-driven instrument head defines a material entry port through which the resected material can enter the flexible endoscopic instrument. A body is coupled to the first proximal end of the power-driven instrument head and configured to drive the power-driven instrument head. The body includes a flexible portion that has a second distal end and a second proximal end. The second proximal end of the flexible portion defines a material exit port. An aspiration channel extends from the material entry port of the power-driven instrument head to the material exit port of the flexible portion. The second proximal end of the flexible portion is configured to couple to a vacuum source such that the resected material entering the aspiration channel via the material entry port is removed from the aspiration channel at the material exit port while the endoscopic instrument is disposed within an instrument channel of a flexible endoscope.

In some implementations, the body further includes a powered actuator. The powered actuator is coupled to the first proximal end of the power-driven instrument head and configured to drive the power-driven instrument head. In some implementations, the powered actuator is one of a hydraulically powered actuator, a pneumatically powered actuator or an electrically powered actuator. In some implementations, the powered actuator includes at least one of an electric motor, a tesla rotor, and a vane rotor. In some implementations, the endoscopic instrument includes an energy storage component configured to power the powered actuator. In some implementations, the aspiration channel is defined by the power-driven instrument head, the powered actuator and the flexible portion.

In some implementations, the powered actuator is one of a hydraulically powered actuator or a pneumatically powered actuator. In some such implementations, the flexible portion includes a fluid inlet tubular member configured to supply irrigation to actuate the power actuator and a fluid outlet tubular member configured to remove the fluid being supplied to actuate the actuator. In some implementations, the flexible portion includes an aspiration tubular member that defines a proximal portion of the aspiration channel.

In some implementations, the powered actuator includes a hollow portion, the hollow portion fluidly coupling the material entry port of the power-driven instrument head and the material exit port of the flexible portion.

In some implementations, the instrument includes an engagement assembly configured to contact the walls of the instrument channel of the endoscope when actuated. In some implementations, the engagement assembly includes a compliant ring structure configured to be deformed.

In some implementations, the power-driven instrument head includes an outer structure and a cutting shaft disposed within the outer structure, the cutting shaft coupled to the powered actuator and configured to rotate relative to the outer structure when the powered actuator is actuated. In some implementations, the cutting shaft includes a hollow portion and the material entry port.

In some implementations, the flexible portion includes a hollow flexible torque cable. The flexible torque cable has a distal region configured to couple to the first proximal end of the power-driven instrument head and has a proximal region configured to couple to a powered actuator. In some implementations, the flexible torque cable defines a portion of the aspiration channel. The distal region of the flexible torque cable is fluidly coupled to the material entry port of the power-driven instrument head and the proximal region of the flexible torque cable includes the material exit port.

In some implementations, the instrument has an outer diameter that is less than about 5 mm. In some implementations, the flexible portion is at least 40 times as long as the power-driven instrument head. In some implementations, the outer diameter of the powered actuator is less than about 4 mm.

According to another aspect, an endoscopic instrument includes a power-driven instrument head configured to resect material at a site within a subject. The power-driven instrument head includes a cutting tip and a material entry port configured to allow material to enter a distal end of the endoscopic instrument. A body is coupled to the power-driven instrument head. The body includes an elongated hollow flexible tubular member that includes a material exit port configured to allow material to exit a proximal end of the endoscopic instrument. An aspiration channel extends from the material entry port of the power-driven instrument head to a material exit port of the elongated hollow flexible tubular member. The second proximal end of the flexible portion is configured to fluidly couple to a vacuum source such that the resected material that enters the aspiration channel via the material entry port of the power-driven instrument head is removed from the endoscopic instrument via the material exit port. The endoscopic instrument is configured to travel through a tortuous instrument channel of an endoscope. In some implementations, the instrument has an outer diameter that is less than about 5 mm and wherein the flexible tubular member is at least 72 inches long.

In some implementations, the body further comprises a powered actuator, the powered actuator coupled to the first proximal end of the power-driven instrument head and configured to drive the power-driven instrument head. In some implementations, the powered actuator is an electrically powered actuator and further comprising an electrically conducting wire configured to couple to a power source. In some implementations, the aspiration channel is defined by the power-driven instrument head, the powered actuator and the flexible portion. In some implementations, the flexible tubular member defines a proximal portion of the aspiration channel.

In some implementations, the powered actuator is one of a hydraulically powered actuator or a pneumatically powered actuator, and further includes a fluid inlet tubular member configured to supply fluid to actuate the power actuator and a fluid outlet tubular member configured to remove the fluid being supplied to actuate the actuator.

In some implementations, the instrument includes an engagement assembly configured to contact the walls of the instrument channel of the endoscope when actuated. In some implementations, the engagement assembly includes a vacuum actuated structure configured to move into an engaged position in which the vacuum actuated structure is not in contact with the instrument channel when the vacuum is actuated and configured to move into a retracted position in which the vacuum actuated structure is not in contact with the instrument channel when the vacuum is not actuated.

In some implementations, the power-driven instrument head includes an outer structure and a cutting shaft disposed within the outer structure, the cutting shaft coupled to the powered actuator and configured to rotate relative to the outer structure when the powered actuator is actuated.

In some implementations, the flexible tubular member includes a hollow flexible torque cable. The flexible torque cable has a distal region configured to couple to the first proximal end of the power-driven instrument head and has a proximal region configured to couple to a powered actuator located external to the endoscopic instrument. In some implementations, the flexible torque cable further defines a portion of the aspiration channel, wherein the distal region of the flexible torque cable is fluidly coupled to the material entry port of the power-driven instrument head and the proximal region of the flexible torque cable includes the material exit port. In some implementations, the instrument includes a sheath surrounding the flexible torque cable.

According to another aspect, a flexible endoscopic biopsy retrieval tool adapted for use with an endoscope includes a housing, a debriding component coupled to the housing, and a sample retrieval conduit disposed within the housing for retrieving debrided material that is debrided by the debriding component. In various embodiments, an improved flexible endoscope may be configured with an integrated endoscopic biopsy retrieval tool that includes a debriding component and a sample retrieval conduit for retrieving debrided material that is debrided by the debriding component.

According to another aspect, a method of retrieving polyps from a patient's body includes disposing an endoscopic instrument within an instrument channel of an endoscope, inserting the endoscope in a patient's body, actuating a debriding component of the endoscopic instrument to cut a polyp within the patient's body, and actuating a sample retrieval component of the endoscopic instrument to remove the cut polyp from within the patient's body.

According to yet another aspect, an endoscope includes a first end and a second end separated by a flexible housing. An instrument channel extends from the first end to the second end and an endoscopic instrument is coupled to the instrument channel at the first end of the endoscope. The endoscopic instrument includes a debriding component and a sample retrieval conduit partially disposed within the instrument channel.

According to yet another aspect, an endoscopic instrument insertable within a single instrument channel of an endoscope includes a cutting assembly that is configured to resect material at a site within a subject. The cutting assembly includes an outer cannula and an inner cannula disposed within the outer cannula. The outer cannula defines an opening through which material to be resected enters the cutting assembly. The endoscopic instrument also includes a flexible outer tubing coupled to the outer cannula and configured to cause the outer cannula to rotate relative to the inner cannula. The flexible outer tubing can have an outer diameter that is smaller than the instrument channel in which the endoscopic instrument is insertable. The endoscopic instrument also includes a flexible torque coil having a portion disposed within the flexible outer tubing. The flexible torque coil having a distal end coupled to the inner cannula. The flexible torque coil is configured to cause the inner cannula to rotate relative to the outer cannula. The endoscopic instrument also includes a proximal connector coupled to a proximal end of the flexible torque coil and configured to engage with a drive assembly that is configured to cause the proximal connector, the flexible torque coil and the inner cannula to rotate upon actuation. The endoscopic instrument also includes an aspiration channel having an aspiration port configured to engage with a vacuum source. The aspiration channel is partially defined by an inner wall of the flexible torque coil and an inner wall of the inner cannula and extends from an opening defined in the inner cannula to the aspiration port. The endoscopic instrument also includes an irrigation channel having a first portion defined between an outer wall of the flexible torque coil and an inner wall of the flexible outer tubing and configured to carry irrigation fluid to the aspiration channel.

In some implementations, the proximal connector is hollow and an inner wall of the proximal connector defines a portion of the aspiration channel. In some implementations, the proximal connector is a rigid cylindrical structure and is configured to be positioned within a drive receptacle of the drive assembly. The proximal connector can include a coupler configured to engage with the drive assembly and a tensioning spring configured to bias the inner cannula towards a distal end of the outer cannula. In some implementations, the tensioning spring is sized and biased such that the tensioning spring causes a cutting portion of the inner cannula to be positioned adjacent to the opening of the outer cannula. In some implementations, the proximal connector is rotationally and fluidly coupled to the flexible torque coil.

In some implementations, the endoscopic instrument also includes a lavage connector including an irrigation entry port and a tubular member coupled to the lavage connector and the flexible outer tubing. An inner wall of the tubular member and the outer wall of the flexible torque coil can define a second portion of the irrigation channel that is fluidly coupled to the first portion of the irrigation channel. In some implementations, the endoscopic instrument also includes a rotational coupler coupling the flexible outer tubing to the tubular member and configured to cause the flexible outer tubing to rotate relative to the tubular member and cause the opening defined in the outer cannula to rotate relative to the inner cannula. In some implementations, the lavage connector defines an inner bore within which the flexible torque coil is disposed.

In some implementations, the endoscopic instrument also includes a lining within which the flexible torque coil is disposed, the outer wall of the lining configured to define a portion of the irrigation channel. In some implementations, the inner cannula is configured to rotate axially relative to the outer cannula and the aspiration channel is configured to provide a suction force at the opening of the inner cannula.

In some implementations, the flexible torque coil includes a plurality of threads. Each of the plurality of threads can be wound in a direction opposite to a direction in which one or more adjacent threads of the plurality of threads is wound. In some implementations, the flexible torque coil includes a plurality of layers. Each of the plurality of layers can be wound in a direction opposite to a direction in which one or more adjacent layers of the plurality of layers is wound. In some implementations, each layer can include one or more threads.

In some implementations, the flexible outer tubing has a length that exceeds the length of the endoscope in which the endoscopic instrument is insertable. In some implementations, the flexible outer tubing has a length that is at least 100 times larger than an outer diameter of the flexible outer tubing. In some implementations, the flexible portion is at least 40 times as long as the cutting assembly.

This Summary is provided to introduce a selection of concepts in a simplified form that are further described below in the Detailed Description. This Summary is not intended to identify key features or essential features of the claimed subject matter, nor is it intended that this Summary be used to limit the scope of the claimed subject matter. Furthermore, the claimed subject matter is not limited to implementations that offer any or all advantages or solve any or all state of the art problems.

BRIEF DESCRIPTION OF THE DRAWINGS

The present disclosure is illustratively shown and described in reference to the accompanying drawing in which:

FIG. 1A illustrates various types of polyps that can form within a body.

FIG. 1B illustrates a perspective partial view of an endoscope according to embodiments of the present disclosure.

FIG. 1C illustrates a perspective view of an endoscopic instrument according to embodiments of the present disclosure.

FIGS. 2A and 2B illustrate side perspective views of an endoscopic instrument coupled with the endoscope shown in FIG. 1 according to embodiments of the present disclosure.

FIGS. 3A and 3B illustrate side perspective views of an example endoscopic instrument coupled with the endoscope shown in FIG. 1 according to embodiments of the present disclosure.

FIG. 4A illustrates an exploded view of the endoscopic instrument that can be coupled with the endoscope according to embodiments of the present disclosure.

FIG. 4B illustrates a perspective view diagram of the endoscopic instrument coupled to the endoscope illustrating the various conduits associated with the endoscopic instrument.

FIG. 5 illustrates a side perspective view of another example endoscopic instrument coupled with the endoscope shown in FIG. 1 according to embodiments of the present disclosure.

FIG. 6 illustrates an enlarged view of an example endoscopic instrument according to embodiments of the present disclosure.

FIG. 7 illustrates a perspective view of an outer blade of a cutting tool of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 8 illustrates a perspective view of an inner blade of the cutting tool of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 9 illustrates a perspective view of a rotor of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 10 illustrates a perspective view of a casing of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 11 illustrates a perspective view of a cap of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 12 illustrates a perspective view of a coupling member of the endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure.

FIG. 13 illustrates a perspective view diagram of the endoscopic instrument coupled to the endoscope illustrating the various conduits associated with the endoscopic instrument.

FIG. 14 illustrates another perspective view diagram of the endoscopic instrument coupled to the endoscope illustrating the various conduits associated with the endoscopic instrument.

FIG. 15 is a conceptual system architecture diagram illustrating various components for operating the endoscopic instrument according to embodiments of the present disclosure.

FIG. 16A illustrates an exploded view of an example endoscopic instrument according to embodiments of the present disclosure.

FIG. 16B illustrates a cross-sectional view of the endoscopic instrument shown in FIG. 16A according to embodiments of the present disclosure.

FIG. 16C illustrates a schematic view of an example engagement assembly of an example endoscopic instrument according to embodiments of the present disclosure.

FIG. 16D shows a cut-open view of the engagement assembly shown in FIG. 16C when the engagement assembly is disengaged according to embodiments of the present disclosure.

FIG. 16E shows a cut-open view of the engagement assembly shown in FIG. 16A when the engagement assembly is configured to engage with an instrument channel of an endoscope according to embodiments of the present disclosure.

FIG. 17A illustrates an exploded view of an example endoscopic instrument according to embodiments of the present disclosure.

FIG. 17B illustrates a cross-sectional view of the endoscopic instrument shown in FIG. 17A according to embodiments of the present disclosure.

FIG. 18A illustrates an exploded view of an example endoscopic instrument utilizing a tesla rotor according to embodiments of the present disclosure.

FIG. 18B illustrates a cross-sectional view of the endoscopic instrument shown in FIG. 18A according to embodiments of the present disclosure.

FIG. 19A illustrates an example endoscopic instrument that is coupled to a powered actuation and vacuum system according to embodiments of the present disclosure.

FIG. 19B illustrates a cross-section view of the powered actuation and vacuum system shown in FIG. 19A according to embodiments of the present disclosure.

FIG. 19C illustrates an exploded view of an example head portion of the endoscopic instrument shown in FIG. 19A according to embodiments of the present disclosure.

FIG. 19D illustrates a cut-open view of a portion of the endoscopic instrument having an engagement assembly according to embodiments of the present disclosure

FIG. 19E shows a cut-open view of the engagement assembly shown in FIG. 19D in a disengaged position according to embodiments of the present disclosure.

FIG. 19F shows a cut-open view of the engagement assembly shown in FIG. 19D in an engaged position according to embodiments of the present disclosure.

FIG. 20 is a conceptual system architecture diagram illustrating various components for operating the endoscopic instrument according to embodiments of the present disclosure.

FIGS. 21AA-21F illustrate aspects of an endoscopic assembly according to embodiments of the present disclosure.

FIGS. 22A-22H show various implementations of example flexible cables according to embodiments of the present disclosure.

FIGS. 23AA-23BB show an example implementation of a cutting tool according to embodiments of the present disclosure.

FIGS. 24A-24C illustrate various aspects of the drive shaft of the coupling component according to embodiments of the present disclosure.

FIG. 25 illustrates an example housing component according to embodiments of the present disclosure.

FIGS. 26A-26E show an example sleeve bearing according to embodiments of the present disclosure.

FIGS. 27A-27C show an example base plate that forms a portion of the casing according to embodiments of the present disclosure.

FIGS. 28A-28D show an example side plate that forms a portion of the casing according to embodiments of the present disclosure.

FIGS. 29AA-29EE show various aspects of ferrules according to embodiments of the present disclosure

FIGS. 30AA-30C illustrate aspects of an endoscopic assembly in which the tip is press-fit according to embodiments of the present disclosure.

FIGS. 31AA-31AB and 31B-31C illustrate aspects of an endoscopic assembly in which the tip is press-fit according to embodiments of the present disclosure.

FIG. 32 shows a top view of an example flexible portion of an endoscopic tool according to embodiments of the present disclosure.

FIG. 33 is a cross-sectional view of an example cutting assembly of an endoscopic tool using a torque rope according to embodiments of the present disclosure.

FIGS. 34A-34C are cross-sectional views of different configurations of the flexible portion region of one implementation of an endoscopic tool described herein.

FIG. 35AA-35AC shows various views of portions of an endoscopic tool according to embodiments of the present disclosure.

FIG. 36 shows a cross-sectional view of the flexible portion region of one implementation of an endoscopic tool according to embodiments of the present disclosure.

FIG. 37 shows a cross-section view of one implementation of the endoscopic tool according to embodiments of the present disclosure.

FIGS. 38A and 38B show various views of a distal portion of one implementation of an endoscopic tool according to embodiments of the present disclosure.

FIGS. 39A and 39B show cross-sectional views of the distal portion of the endoscopic tool shown in FIGS. 38A and 38B along the sections B-B and sections C-C according to embodiments of the present disclosure.

FIG. 40A shows a perspective view of an endoscopic tool and a portion of a drive assembly configured to drive the endoscopic tool according to embodiments of the present disclosure.

FIG. 40B shows a perspective view of the endoscopic tool and the portion of the drive assembly configured to drive the endoscopic tool shown in FIG. 40A according to embodiments of the present disclosure.

FIG. 41 shows a top view of the endoscopic tool and a top exposed view of the portion of the drive assembly shown in FIGS. 40A-40B according to embodiments of the present disclosure.

FIG. 42 shows a cross-sectional view of the endoscopic tool and the portion of the drive assembly across the section A-A shown in FIGS. 40A-40B according to embodiments of the present disclosure.

FIG. 43 shows an enlarged view of the drive connector of the endoscope and the portion of the drive assembly shown in FIGS. 40A-40B according to embodiments of the present disclosure.

FIG. 44 shows a perspective view of the endoscopic tool and a portion of the drive assembly shown in FIGS. 40A-40B according to embodiments of the present disclosure.

FIG. 45 shows a cross-sectional view of the endoscopic tool and the portion of the drive assembly across the section B-B according to embodiments of the present disclosure.

FIG. 46 shows an enlarged cross-sectional view of the rotational coupler section of the endoscopic tool according to embodiments of the present disclosure.

FIG. 47A and FIG. 47B show a top view and a cross-sectional view of the rotational coupler of the endoscopic tool according to embodiments of the present disclosure.

FIG. 48 is a perspective view of a portion of the endoscopic tool inserted for operation within a drive assembly according to embodiments of the present disclosure.

FIG. 49 illustrates another implementation of the endoscopic tool and a drive assembly configured to drive the endoscopic tool according to embodiments of the present disclosure.

FIG. 50A is a side view of the endoscopic tool and drive assembly shown in FIG. 49 according to embodiments of the present disclosure.

FIG. 50B is a cross-sectional view of the endoscopic tool and drive assembly shown in FIG. 49 taken along the section A-A according to embodiments of the present disclosure.

FIG. 51 is a schematic diagram of a surgical system including a surgical instrument having an improved flexible outer tubing according to embodiments of the present disclosure.

FIG. 52 is a cross-section view of the improved flexible outer tubing of FIG. 51 according to embodiments of the present disclosure.

DETAILED DESCRIPTION A. Improved Endoscopic Instrument Systems and Methods

Technologies provided herein are directed towards an improved flexible endoscopic instrument that can precisely and efficiently obtain samples of single and multiple polyps and neoplasms from a patient. In particular, the improved endoscopic instrument is capable of debriding samples from one or more polyps and retrieving the debrided samples without having to remove the endoscopic instrument from the treatment site within the patient's body.

FIG. 1A illustrates various types of lesions that can form within a body. Many polyps may be removed by snare polypectomy, though especially large polyps and/or sessile or flat polyps must be removed piecemeal with biopsy forceps or en bloc using endoscopic mucosal resection (EMR). A recent study has concluded that depressed sessile polyps had the highest rate for harboring a malignancy at 33%. The same study has also found that non-polypoid neoplastic lesions (sessile polyps) accounted for 22% of the patients with polyps or 10% of all patients undergoing colonoscopy. There are multiple roadblocks to resecting colon polyps, namely the difficulties in removing sessile polyps, the time involved in removing multiple polyps and the lack of reimbursement differential for resecting more than one polyp. Since resecting less accessible sessile polyps presents challenges and multiple polyps take more time per patient, most polyps are removed piece meal with tissue left behind as polyps increase in size, contributing to a sampling bias where the pathology of remaining tissue is unknown, leading to an increase in the false negative rate.

Colonoscopy is not a perfect screening tool. With current colonoscopy practices the endoscopist exposes the patient to sample bias through piecemeal EMR sessile/flat polyps. Sessile polyps are extremely difficult or impossible to remove endoscopically with current techniques and often incompletely resected. Current colonoscopy instruments for polyp resection are limited by their inability to adequately remove sessile polyps and inefficiency to completely remove multiple polyps. Sessile polyp fragments that are left behind after incomplete resection will grow into new polyps and carry risks for malignancy. Physicians treating lesions in other parts of a subject's body face similar issues, for instance, Barrett's esophagus, and pulmonary tumors among others.

In the recent past, endoscopic mucosal resection (EMR) has been adopted to remove sessile polyps. EMR involves the use of an injection to elevate surrounding mucosa followed by opening of a snare to cut the polyp and lastly use of biopsy forceps or a retrieval device to remove the polyp. The introduction and removal of the injection needle and snare through the length of the colonoscope, which is approximately 5.2 feet, must be repeated for the forceps.

The present disclosure relates to an endoscopic tool that is capable of delivering an innovative alternative to existing polyp removal tools, including snares, hot biopsy and EMR, by introducing a flexible powered instrument that that works with the current generation colonoscopes and can cut and remove any polyp. The endoscopic tool described herein can be designed to enable physicians to better address sessile or large polyps as well as remove multiple polyps in significantly less time. Through the adoption of the endoscopic tool described herein, physicians can become more efficient at early diagnosis of colorectal cancer.

The present disclosure will be more completely understood through the following description, which should be read in conjunction with the drawings. In this description, like numbers refer to similar elements within various embodiments of the present disclosure. Within this description, the claims will be explained with respect to embodiments. The skilled artisan will readily appreciate that the methods, apparatus and systems described herein are merely exemplary and that variations can be made without departing from the spirit and scope of the disclosure.

Referring back to the drawings, FIG. 1B illustrates a perspective partial view of an endoscope according to embodiments of the present disclosure. Although the present disclosure is directed towards endoscopic instruments adapted for use with any type of endoscope, for sake of convenience, the teachings of the present disclosure are directed towards endoscopic instruments used with a lower GI scope, such as a colonoscope. It should, however, be appreciated that the scope of the present disclosure is not limited to endoscopic instruments for use with GI scopes, but extends to any type of flexible endoscope, including but not limited to bronchoscopes, gastroscopes and laryngoscopes, or other medical devices that may be used to treat patients.

According to various embodiments, a typical lower GI scope 100 includes a substantially flexible member that extends from a first end or head portion 102 to a second end or handle portion. The head portion 102 may be configured to swivel so as to orient a tip 104 of the head portion 102 in any direction within a hemispherical space. The handle portion has controls that allows the operator of the endoscope 100 to steer the colonoscope towards an area of interest within the colon and turn the corners between colon segments with two steering wheels.

A series of instruments reside on the face 106 of the scope's tip 104, including but not limited to, one or more water channels 108A-108N, generally referred to as water channels 108, for irrigating the area with water, one or more light sources 110A-110N, generally referred to as light sources 110, a camera lens 112, and an instrument channel 120 through which an endoscopic instrument can be passed through to conduct a number of operations. The instrument channel 120 can vary in size based on the type of endoscope 100 being used. In various embodiments, the diameter of the instrument channel 120 can range from about 2 mm to 6 mm, or more specifically, from about 3.2 mm to 4.3 mm. Some larger scopes may have two instrument channels 120 so that two tools can be passed into the patient simultaneously. However, larger scopes may cause discomfort to the patient and may be too large to enter the patient's body through some of the smaller cavities.

FIG. 1C illustrates a perspective view of an endoscopic instrument 150 according to embodiments of the present disclosure. The endoscopic instrument 150 is configured to be fed through the instrument channel 120 of the endoscope 100 depicted in FIG. 1B. The endoscopic instrument 150 is configured to be inserted within an instrument channel of an endoscope, such as the instrument channel 120 of the endoscope 100 depicted in FIG. 1B. In some implementations, the portion of the endoscopic instrument 150 that is configured to be inserted within the instrument channel 120 may be sized to have an outer diameter that is smaller than the inner diameter of the instrument channel 120 of the endoscope. In some such implementations, the endoscopic instrument 150 can be sized to have an outer diameter that is sufficiently small to be slidably inserted within the instrument channel while the endoscope is coiled or bent. When the endoscope is coiled or bent, the instrument channel can form a tortuous path that includes one or more curves and bends. In one example implementations, an endoscope includes an instrument channel that has an inner diameter of about 4.3 mm when the endoscope is straightened. However, when the endoscope is coiled or bent, portions of the endoscope near the bends can have clearances that are smaller than the inner diameter of about 4.3 mm. In some implementations, the endoscope can have clearances that may be about 3.8 mm instead of the 4.3 mm achieved when the endoscope is straightened. In some implementations, the endoscope can have clearances that may be about 3.2 mm. As such, in some implementations, the endoscopic instrument 150 may be sized such that it can be slidably inserted within the instrument channel of the endoscope with which it is to be used even when the endoscope is coiled or bent.

In some implementations, the endoscopic instrument 150 includes a power-driven instrument head 160 configured to resect material at a site within a subject. The power-driven instrument head 160 has a distal end 162 and a proximal end 161. The distal end 162 of the power-driven instrument head 160 defines a material entry port 170 through which the resected material can enter the endoscopic instrument 150. The power-driven instrument head 160 can include a cutting section at the distal end 162 that is configured to cut tissue and other material. As used herein, a port can include any opening, aperture, or gap through which material can either enter or exit. In some implementations, the material entry port can be an opening through which resected material can enter the endoscopic instrument 150. In some implementations, material to be resected can be suctioned into the material entry port where the instrument head can then resect the material.

A body 152 includes a head portion 155 and a flexible portion 165. A distal end 156 of the head portion 155 of the body 152 is coupled to the proximal end 161 of the power-driven instrument head 160. In some implementations, the head portion 155 of the body 152 is configured to drive the power-driven instrument head 160. A proximal end 158 of the head portion 155 can be coupled to a distal end 166 of the flexible portion 165. A proximal end 176 of the flexible portion 165 defines a material exit port 175. The flexible portion 165 can include a hollow flexible tubular member.

The endoscopic instrument also includes an aspiration channel that extends from the material entry port 170 of the power-driven instrument head 160 to the material exit port 175 of the flexible portion 165. In some implementations, the aspiration channel is defined by the power-driven instrument head 160, the head portion 155 of the body 152 and the flexible portion 165 of the body. The proximal end 176 of the flexible portion 165 is configured to couple to a vacuum source such that the resected material entering the aspiration channel via the material entry port 170 is removed from the aspiration channel at the material exit port 175 while the endoscopic instrument 150 is disposed within an instrument channel of an endoscope.

The head portion 155 includes a housing that has an outer diameter that is configured such that the endoscopic instrument 150 can be slidably inserted into an instrument channel of an endoscope. In some implementations, the head portion 155 can include a powered actuator that is configured to drive the power-driven instrument head 160. In some implementations, the powered actuator is disposed within the head portion 155. In some implementations, the powered actuator is located external to the portion of the endoscopic instrument 150 that can be inserted into an instrument channel of an endoscope. In some implementations, the powered actuator is capable of driving the power-driven instrument head via a shaft that can translate motion generated by the power actuator to the power-driven instrument head. In some implementations, the powered actuator is not a part of the endoscopic instrument 150, but instead, is coupled to the power-driven instrument head 160. In some implementations, the shaft may be a flexible shaft. In some such implementations, the flexible shaft can be a flexible torque coil, additional details of which are provided below with respect to FIGS. 19A-19C.

The endoscopic instrument 150 can be sized to be insertable within an instrument channel of an endoscope. In some implementations, the endoscopic instrument 150 may be sized such that the endoscopic instrument can be inserted within the instrument channel of the endoscope while the endoscope is inserted within a subject. In some such implementations, the endoscope, for example, a colonoscope, may be curved or bent thereby requiring the endoscopic instrument 150 to be sized such that it can be inserted into a curved or bent endoscope.

In some implementations, the head portion 155 and the power-driven instrument head 160 of the endoscopic instrument 150 may be substantially stiff or rigid, while the flexible portion 165 may be relatively flexible or compliant. The head portion 155 and the power-driven instrument head 160 can be substantially rigid. As such, in some such implementations, the head portion 155 and the power-driven instrument head 160 may be sized, at least in thickness and in length, such that endoscopic instrument 150 can maneuver through sharp bends and curves during insertion of the endoscopic instrument 150 within the instrument channel of the endoscope. In some implementations, the length of the power-driven instrument head 160 may be between about 0.2″-2″, about 0.2″ and 1″ or in some implementations, between 0.4″ and 0.8″. In some implementations, the outer diameter of the power-driven instrument head 160 may be between about 0.4″-1.5″, 0.6″ and 1.2″ and 0.8″ and 1″. In some implementations, the length of the head portion 155 of the body may be between about 0.5″-3″, about 0.8″ and 2″ and 1″ and 1.5″.

The length of the flexible portion 165 may be substantially and/or relatively longer than the length of the head portion and the power-driven instrument head 160. In some implementations, the flexible portion 165 can be sufficiently long such that the combined length of the endoscopic instrument exceeds the length of instrument channel of an endoscope in which the instrument can be inserted. As such, the length of the flexible portion 165 may have a length that exceeds about 36″, about 45″ or about 60″. For endoscopic instruments configured for use with other types of endoscopes, the length of the flexible portion may be shorter than 36″, but still sufficiently long to allow for the body of the endoscopic instrument to be approximately the same length or greater than the length of the endoscope with which the instrument is being used.

The outer diameter of the flexible portion 165 can also be configured such that the endoscopic instrument can be inserted into the instrument channel of the endoscope. In some implementations, the outer diameter of the flexible portion 165 can be sized smaller than a corresponding inner diameter of the instrument channel of the endoscope. In some such implementations, the endoscopic instrument can be sized to have an outer diameter that is sufficiently small to be slidably disposed within the endoscope while the endoscope is coiled or bent. For example, an endoscope can include an instrument channel that has an inner diameter of about 4.3 mm when the endoscope is straightened. However, when the endoscope is coiled or bent, portions of the endoscope near the bends can have clearances that are smaller than the inner diameter of about 4.3 mm. In some implementations, the endoscope can have clearances that may be as low as 3.2 mm. As such, in some implementations, the endoscopic instrument may be sized such that the endoscopic instrument can be slidably inserted within the instrument channel of the endoscope even when the endoscope is coiled or bent.

FIGS. 2A and 2B and 3A and 3B illustrate side perspective views of an endoscopic instrument coupled with the endoscope shown in FIG. 1B according to embodiments of the present disclosure. The endoscopic instrument 220 is configured to be fed through the instrument channel 120 of the endoscope 100. As shown in FIGS. 2A and 2B, the endoscopic instrument 220 is capable of extending outside the tip 104 of the endoscope 100, while FIGS. 3A and 3B show that the endoscope tool 220 can be retracted within the endoscope such that no part of the endoscopic instrument 220 is extending beyond the tip 104 of the endoscope 100. As will be described in further detail with respect to FIG. 4, the endoscopic instrument 220 is capable of cutting or debriding a polyp as well as obtaining the debrided polyp from the treatment site without having to remove the endoscopic instrument 220 from the endoscope 100.

FIG. 4A illustrates an exploded view of the endoscopic instrument 220 adapted for use with the endoscope 100 according to embodiments of the present disclosure. The endoscopic instrument 220 includes a debriding component for debriding polyps grown in the patient's body, and a sample retrieval component for retrieving the debrided polyps from the surgical site. The endoscopic instrument 220 includes a tubing 410 coupled to a cap 420. In various embodiments, the cap 420 may be sealingly engaged with the tubing 410. The cap can be aligned with a spindle 430 at a first portion of the spindle 430. In various embodiments, the spindle 430 may be substantially hollow. The spindle 430 can be coupled to a rotor 440, which is configured to rotate the spindle 430. A second portion of the spindle 430 includes an inner blade 450 that may be configured to interact with an outer blade 460. In some implementations, the outer blade 460 can be separated from the inner blade by a gap that forms an irrigation channel (not shown). A casing 470 is configured to encompass the cap 420 and the rotor 440, as shown above with respect to FIGS. 2A and 3A. It should be appreciated that other components, such as washers, bearings, seals, and the like, may be included in the endoscopic instrument 220.

FIG. 4B is a schematic diagram of an endoscopic instrument partially inserted within an instrument channel of an endoscope endoscopic instrument. In various embodiments, the cap, connector, rotor and casing may be made from injection molded plastic. The spindle and the cannula may be made from surgical grade steel, and the tubing may be made from silicone. However, it should be appreciated that these materials are merely examples of materials that can be used. Those skilled in the art will appreciate that other materials may be used instead of the ones described above.

The tubing 410 in FIG. 4A may be sized to pass through the instrument channel 120 of the endoscope 100 in FIGS. 4A and 4B. The tubing 410 may include one or more pneumatic fluid entry conduits 412, one or more pneumatic fluid exit conduits 414, one or more irrigation conduits 416, and one or more suction conduits 418. The pneumatic fluid entry conduits 412 arc configured to supply pressurized air to pneumatically drive the rotor 440, while the pneumatic fluid exit conduits 414 remove the air supplied by the pneumatic fluid entry conduits 412 to prevent a large amount of air from entering the patient's body. The irrigation conduits 416 supply an irrigation fluid, such as water, between the inner blade 450 and the outer blade 460 to help lubricate the area between the inner blade 450 and the outer blade 460. In addition, the irrigation fluid then flows from the outside of the inner blade 450 to the inside portion of the inner blade 450. It should be appreciated that the inside portion of the inner blade 450 may be aligned with the suction conduit 418 of the tubing 410 via the cap 420 such that any fluid that enters the inner blade 450 can pass through the inner blade 450 into the suction conduit 418 of the tubing 410. The irrigation fluid that flows through the inside portion of the inner blade 450 and the suction conduit 418 helps lubricate the suction conduit 418, through which the debrided polyps and other waste from the patient's body are removed. As described above, the tubing 410 is coupled to the cap 420 at a first end, but is coupled to one or more components at a second end (not shown). For instance, at the second end, the pneumatic air entry conduits 412 may be coupled to a compressed air source, while the irrigation fluid conduit 416 may be coupled to a water supply source. In addition, the pneumatic fluid exit conduits 414 may be coupled to the compressed air source or simply left exposed outside the patient's body for venting.

In various embodiments, the suction conduit 418 may be coupled to a disposable cartridge that is configured to catch the cut polyps and store them for examination at a later time. In various embodiments, the disposable cartridge may include multiple collection bins. The operator may be capable of selecting the collection bin in which to collect a sample of a particular cut polyp. Upon selecting the collection bin, the suction conduit 418 supplies the collected material from within the patient's body to the particular collection bin. As such, the operator may be able to collect samples for each polyp in individual collection bins. In this way, the cancerous nature of individual polyps can be determined.

The cap 420 may be sized to fit within the first end of the tubing 410. In various embodiments, the first end of the tubing 410 may include a connector that is configured to couple with the cap 420. In various embodiments, the cap 420 may be press fitted into the connector of the tubing 410. As such, the cap 420 may include corresponding conduits that match the conduits of the tubing 410. Accordingly, compressed air from the compressed air source may be supplied through the pneumatic air entry conduits 412 of the tubing 410 and corresponding pneumatic air entry conduits of the cap 420 towards the rotor 440. The rotor 440 may include one or more rotor blades 442 on which the compressed air is impinged thereby causing the rotor 440 to rotate. The air impinging on the rotor blades 442 may then exit through the corresponding pneumatic air exit conduits of the cap and the pneumatic air entry conduits 414 of the tubing 410. The speed at which the rotor 440 can rotate depends on the amount of air and the pressure at which the air is supplied to the rotor 440. In various embodiments, the speed at which the rotor 440 rotates may be controlled by the operator of the endoscope 100. Although the present disclosure discloses pneumatic means for operating the rotor, some embodiments may include hydraulic means for operating the rotor. In such embodiments, a fluid, such as water, may be supplied in lieu of compressed air, in the pneumatic air entry conduit 412.

As described above, the spindle 430 is coupled to the rotor 440, such that when the rotor 440 rotates, the spindle 430 also rotates. In various embodiments, the first end of the spindle 430 includes the inner blade 450, which correspondingly, also rotates along with the rotor 440. The inner blade 450 may be sized to fit within the diameter of the outer blade 460. In various embodiments, irrigation fluid supplied from an irrigation fluid source may be supplied through the irrigation fluid conduit 416 of the tubing 410 and the corresponding conduit of the cap 420, along the space between the inner blade 450 and the outer blade 460, and into the suction conduit 418 defined by the inner diameter of the inner blade 450. It should be appreciated that since the suction conduit 418 is coupled to a vacuum source, fluids and other material may be suctioned through the suction conduit. In this way, the irrigation fluid is able to lubricate at least a substantial length of the suction conduit 418, from the tip 452 of the inner blade 450, through the spindle 430, cap 420, and tubing 410 into the disposable cartridge described above.

The inner blade 450 may rotate relative to the outer blade 460 such that the interaction between the inner blade 450 and the outer blade 460 causes polyps to be cut upon contact with the inner blade 450. In various embodiments, other mechanisms for cutting polyps may be utilized, which may or may not include the use of a rotor 440, inner blade 450 or outer blade 460.

The debriding component may generally be configured to debride a polyp. Debriding can, for example, include any action involving detaching the polyp or a portion of the polyp from a surface of the patient's body. Accordingly, actions, including but not limited to, cutting, snaring, shredding, slicing, shattering, either entirely or partially, are also examples of debriding. Accordingly, the debriding component may be a component that is capable of cutting, snaring, shredding, slicing, shattering, a polyp from a surface of the patient's body. As such, the debriding component may be implemented as a forceps, scissor, knife, snare, shredder, or any other component that can debride a polyp. In some embodiments, the debriding component may be manually actuated such that the debriding component may be operated through the translation of mechanical forces exerted by an operator or automatically actuated, using a turbine, electrical motor, or any other force generating component to actuate the debriding component. For instance, the debriding component may be actuated hydraulically, pneumatically, or electrically. In various embodiments, a separate conduit passing through the tubing or a channel of the endoscope may be configured to carry an electrical wire to provide power to the electrically powered actuator, such as an electrical motor.

According to various embodiments, the debriding component may include a turbine assembly, which is made up of the rotor 440, the rotor blades 442, and the spindle 430. The operator may actuate the debriding component of the endoscopic instrument by supplying compressed air to the turbine assembly. When the operator is ready to begin debriding the polyp, the operator actuates the turbine assembly causing the debriding component to be actuated. In embodiments, such as the embodiment disclosed in FIG. 4, actuating the debriding component may constitute causing the inner blade 450 to rotate relative to the outer blade 460. Upon actuation, the operator may bring the endoscopic instrument 220 towards the polyp to be debrided causing the inner blade 450 to debride the polyp, causing portions of the debrided polyp to lie in the vicinity around the area where the polyp had grown. The operator may then de-actuate the turbine assembly and actuate suction through the suction conduit 418. The operator may then bring the inner blade close to the cut polyp causing the cut polyp to be retrieved through the suction conduit 418. In various embodiments, the suction component of the endoscopic instrument may be actuated while the debriding component is actuated, thereby allowing any debrided material to be retrieved by the suction component.

Although the above embodiment houses a debriding component that utilizes a turbine assembly, the scope of the present disclosure is not limited to such embodiments. Rather, it should be appreciated by those skilled in the art that the debriding component may be manually operated or may utilize any other means of debriding a polyp such that the debrided polyps are capable of being retrieved from the surgical site via the suction conduit described above. Accordingly, examples of debriding components may include, but are not limited to, snips, blades, saws, or any other sharp tools that may or may not be driven by a turbine assembly. It should be appreciated that using a debriding component that is able to cut a polyp into small enough pieces may be desirable such that the cut pieces may be retrieved via the suction conduit without having to remove the endoscopic instrument from the endoscope.

The geometry and assembly of the turbine assembly for rotating at least one of the cutting tool blades may be based on fluid dynamics. Bernoulli's equation can be used to explain the conversion between fluid pressure and the fluid velocity. According to this equation, the fluid velocity is related to the initial fluid pressure by the equation:

$V = \sqrt{2*\frac{P}{D}}$

where V is Velocity, P is Pressure, and D is Mass density.

In order for the fluid to reach the calculated velocity, the fluid can be developed at the point of exit such that the channel through which the fluid is flowing meets an empirically determined L/D ratio of 2, where ‘D’ is the wetted diameter of the flow and the ‘L’ is the length of the channel.

To further understand the interaction of the rotor blades and the fluid, it is assumed that the rotor blade is made so that the air jet impinges the rotor blade on a plane. The equation of linear momentum can be applied to find the forces generated:

${\sum F} = {{\frac{d}{dt}\left( {\int{\int{\int{{Vp}*{{dVol}.}}}}} \right)} + {\sum{()}_{out}} - {\sum()_{in}}}$

where:

is the mass flow of the impinging air jet, and V is Volume.

Assuming that the control volume remains constant (volume between blades), the force created on the blade can be solved for:

ΣF=

−V _(in))

The quantity V_(out) and V_(in) are the same in an impulse turbine, the momentum change being created by the changing direction of the fluid only. The mass flow

is defined by the pump that is to be specified. The actual numerical value also needs to account for the velocity of the rotor. So finally, the force generated by a single blade-air jet interaction is:

ΣF=

−V _(rotor))−(V _(jet) −V _(rotor))cos θ)

ΣF=

−V _(rotor))(1−cos θ)

where ‘θ’ is the difference of the angle between the incoming air jet to that of the exiting air jet. Thought theoretically, the maximum amount of torque can be generated by a ‘θ’ value of 180°, but doing so will actually send the incoming jet onto the back of the following blade. Accordingly, the angle is best given a design value 15° to 20° below 180 to allow a fluid a clean exit. Finally, the force can be defined into a rotational torque:

ΣT=(

r)(V _(jet) −V _(rotor))(1−cos θ)

A second force that can be considered comes from redirecting the air jet from the nozzle into the turbine wheel. To power the turbine, the air jet can be turned 90° into the direction of the blades from the direction of the air jet. The turning of the air jet will create a force on the stationary housing that is a function of the jet velocity, which in turn is proportional to the applied pressure:

ΣF=

This force can be reacted by the connection between the housing and the endoscope, a failure to do so can result in the ejection of the turbine assembly during operation.

Computational analyses based on Finite Element Methods (FEM) reveal that the areas where the greatest stresses are found are located near the root of the blade where a sharp corner is located. The design of air input channel can be simplified by the existing air nozzle channel in endoscope. The air nozzle in existing endoscopes directs pressurized air across objective lens to remove moisture and also provides distension of a cavity being examined or directs pressurized water across objective lens to clear debris.

Referring now to FIG. 4B, a perspective view diagram of the endoscopic instrument coupled to the endoscope illustrating the various conduits associated with the endoscopic instrument is shown. In particular, the pneumatic air entry conduit 412 is shown supplying pressurized air to the rotor assembly, while the pneumatic air exit conduit 412 (not shown in this view) removes the air from the rotor assembly to outside the endoscope 100. The irrigation channel 416 is shown to carry irrigation fluid into the endoscopic instrument 220, where the irrigation fluid enters into the suction conduit 418, which carries material from within the patient's body to a collection component outside the endoscope. As shown in FIG. 4B, the irrigation fluid may enter the suction conduit 418 at an irrigation fluid entry opening 419. It should be appreciated that the placement of the irrigation fluid entry opening 419 may be placed anywhere along the suction conduit. Due to the suction force being applied to the suction conduit, irrigation fluid may be forced into the suction conduit without the risk of the materials flowing in the suction conduit from flowing outside the suction conduit through the irrigation fluid entry opening 419. Moreover, in some embodiments, the irrigation channel may only supply irrigation fluid to the endoscopic instrument while suction is being applied to the suction conduit.

FIG. 5 illustrates a side perspective view of another endoscopic instrument coupled with the endoscope shown in FIG. 1 according to embodiments of the present disclosure. The add-on endoscopic instrument 500 is sized to couple with the walls defining the instrument channel 120 of the tip 104 of the endoscope 100. In various embodiments, the add-on endoscopic instrument 500 may be removably attached to the instrument channel 120 of the endoscope 100 at the tip 104 of the endoscope 104 by way of an interference fit or a press fit. In other embodiments, the add-on endoscopic instrument 500 may be coupled to the endoscope 100 using other attachment means known to those skilled in the art.

Referring now to FIG. 6, an enlarged view of the add-on endoscopic instrument 500 is shown. The add-on endoscopic instrument includes an outer blade or support member 510, an inner blade 520 disposed within the outer blade 510, a rotor 530 coupled to the inner blade 520 and encompassed by a casing 540. The casing is coupled to a cap 550, which is further coupled to a connector 560. In some embodiments, the connector 560 may be sized to engage with the inner diameter of the instrument channel 120 of the endoscope 100. In some embodiments, any other component of the endoscopic instrument may be configured to engage with the endoscope 100 in such a manner as to secure the endoscopic instrument to the instrument channel 120.

FIGS. 7-12 illustrate perspective views of the individual components of the add-on endoscopic instrument shown in FIG. 6 according to embodiments of the present disclosure. In contrast to the endoscopic instrument 220 disclosed with respect to FIGS. 1-4, the add-on endoscopic instrument 500 may be adapted to fit within a first end of instrument channel 120 of the endoscope 100.

In various embodiments, a second end of the instrument channel 120 may be coupled to a vacuum source, which causes material to be suctioned through the instrument channel 120. A suction conduit extends from the vacuum source through the instrument channel of the endoscope, and further through the connector 560, the cap 550, and the rotor 530, to a first end of the inner blade 520, which has an opening defined by the inner diameter of the inner blade 520. It should be appreciated that the connector 560, the cap 550, the casing 540, and the rotor 530 have respective center bores 566, 556, 546 and 536 that are aligned such that materials are allowed to flow from the opening of the inner blade 520 to the vacuum source via the second end of the instrument channel 120.

In addition, the casing 540 of the add-on endoscopic instrument 500 includes a pneumatic air entry port 542 and a pneumatic air exit port 544 as shown in FIG. 10. The pneumatic air entry port 542 may be adapted to receive compressed air from a compressed air source through a pneumatic air entry conduit that passes along the length of the endoscope 100 to outside the patient's body, while the pneumatic air exit port 544 may be adapted to vent air that is impinged on the rotor 530 through a pneumatic air exit conduit that passes along the length of the endoscope 100 to outside the patient's body. In this way, the rotor may be actuated by supplying compressed air from the compressed air source, as described above with respect to FIGS. 1-4. It should be appreciated that although the rotor and associated components disclosed herein describe the use of pneumatic air, the rotor may be driven hydraulically. In such embodiments, the pneumatic air conduits may be configured to carry a liquid, such as water, to and from the area around the rotor.

Referring now also to FIG. 13, it should be appreciated that the pneumatic air entry and exit conduits may extend from the add-on endoscopic instrument to a pneumatic air source through the instrument channel 120 of the endoscope 100. In such embodiments, a tubing that includes separate conduits for the pneumatic air entry and exit conduits and the suction conduit may extend from outside the endoscope to the add-on endoscopic instrument within the endoscope. The tubing may be capable of being fed through the instrument channel of the endoscope and coupled to the add-on endoscopic instrument 500. In such embodiments, the add-on endoscopic instrument 500 may be configured with an additional component that has predefined channels that couple the respective channels of the tubing with the associated with the pneumatic air entry and exit openings of the add-on endoscopic instrument and the suction conduit formed within the add-on endoscopic instrument. In addition, an irrigation fluid channel may also be defined within the tubing such that irrigation fluid may be supplied to the add-on endoscopic instrument 500, from where the irrigation fluid is diverted into the suction conduit.

In various embodiments, the tip of the outer blade 510 may be sharp and may cause discomfort to the patient while entering a cavity of the patient's body. As such, a guard structure (not shown), such as a gel cap or other similar structure, may be attached to the outer blade prior to inserting the add-on endoscopic instrument into the patient's body to prevent injuries from the outer blade contacting a surface of the patient's body. Once the endoscopic instrument is inserted in the patient's body, the guard structure may be released from the outer blade 510. In various embodiments, the guard structure may dissolve upon entering the patient's body.

Referring now to FIG. 14, an improved endoscope having a built in polyp removal assembly is shown according to embodiments of the present disclosure. The improved endoscope 1400 may be similar to conventional endoscopes in many aspects, but may differ in that the improved endoscope may include a built in polyp removal assembly 1440 within an instrument channel of the endoscope 1400. The polyp removal assembly 1440 may include a turbine assembly having a rotor 1442 with rotor blades sealed in a casing 1444 that has one or more inlet and outlet ports for allowing either pneumatic or hydraulic fluid to actuate the rotor 1442. The inlet ports may be designed such that the fluid may interact with the rotor blades at a suitable angle to ensure that the rotor can be driven at desired speeds.

In addition, the polyp removal assembly 1440 may be coupled to a connector 1420, which is configured to couple the polyp removal assembly 1440 to a tubing 1470. The tubing 1470 may include a pneumatic air entry conduit 1412, a pneumatic air exit conduit (not shown), an irrigation fluid conduit 1416 and a suction conduit 1418 that passes through the center of the turbine assembly. The tubing 1440 may be sized such that the tubing 1440 can be securely coupled to the connector 1420 such that one or more of the conduits of the tubing 1440 are coupled to corresponding conduits within the connector 1440. The connector 1420 may be designed to include an irrigation fluid entry opening 419, which allows irrigation fluid to pass into the suction conduit 1418 of the tubing 1440 when the tubing is coupled to the connector.

The turbine assembly of the endoscope 1400 may be configured to couple with a removable debriding assembly 1460, which includes a spindle and a cannula, in a manner that causes the debriding assembly to be operational when the turbine assembly is operating.

In other embodiments of the present disclosure, an endoscope may be designed to facilitate debriding one or more polyps and removing the debrided material associated with the polyps in a single operation. In various embodiments, the endoscope may include one or more separate channels for removing debrided material, supplying irrigation fluid, and supplying and removing at least one of pneumatic or hydraulic fluids. In addition, the endoscope may include a debriding component that may be fixedly or removably coupled to one end of the endoscope. In various embodiments, based on the operation of the debriding component, a separate debriding component channel may also be designed for the debriding component. In addition, the endoscope may include a light and a camera. In one embodiment, the endoscope may utilize existing channels to supply pneumatic or hydraulic fluids to the actuator of the endoscopic instrument for actuating the debriding component. For instance, in the endoscope shown in FIG. 1, the water channels 108A-N may be modified to supply fluids to the actuator pneumatically or hydraulically. In such embodiments, the endoscopic instrument may include a connector having a first end capable of being coupled to an opening associated with existing channels 108 of the endoscope, while another end of the connector is exposed to an opening at the actuator.

In various embodiments of the present disclosure, the endoscopic instrument may further be configured to detect the presence of certain layers of tissue. This may be useful for physicians to take extra precautions to prevent bowel perforations while debriding polyps. In some embodiments, the endoscopic instrument may be equipped with a sensor that can communicate with a sensor processing component outside the endoscope to determine the type of tissue. The sensor may gather temperature information as well as density information and provide signals corresponding to such information to the sensor processing unit, which can identify the type of tissue being sensed. In some implementations, the sensor may be an electrical sensor.

In addition, the endoscopic instrument may be equipped with an injectable dye component through which a physician may mark a particular region within the patient's body. In other embodiments, the physician may mark a particular region utilizing the debriding component, without the use of an injectable dye.

Although the present disclosure discloses various embodiments of an endoscopic instrument, including but not limited to a tool that may be attached to the tip of the endoscope, and a tool that may be fed through the length of the endoscope, the scope of the present disclosure is not intended to be limited to such embodiments or to endoscopic instruments in general. Rather, the scope of the present disclosure extends to any device that may debride and remove polyps from within a patient's body using a single tool. As such, the scope of the present disclosure extends to improved endoscopes that may be built with some or all of the components of the endoscopic instruments described herein. For instance, an improved endoscope with an integrated turbine assembly and configured to be coupled to a debriding component is also disclosed herein. Furthermore, the endoscope may also include predefined conduits that extend through the length of the endoscope such that only the suction conduit may be defined by a disposable tubing, while the air entry and exit conduits and the irrigation conduit are permanently defined within the improved endoscope. In other embodiments, the suction conduit is also predefined but made such that the suction conduit may be cleaned and purified for use with multiple patients. Similarly, the debriding component may also be a part of the endoscope, but also capable of being cleaned and purified for use with multiple patients. Furthermore, it should be understood by those skilled in the art that any or all of the components that constitute the endoscopic instrument may be built into an existing endoscope or into a newly designed endoscope for use in debriding and removing polyps from within the patient's body.

Referring now to FIG. 15, a conceptual system architecture diagram illustrating various components for operating the endoscopic instrument according to embodiments of the present disclosure is shown. The endoscopic system 1500 includes an endoscope 100 fitted with an endoscopic instrument 220, and which may be coupled to an air supply measurement system 1510, an irrigation system 1530 and a polyp removal system 1540. As described above, the tubing that extends within the endoscope 100 may include one or more pneumatic air entry conduits 412 and one or more pneumatic air exit conduits 414. The pneumatic air entry conduits 412 are coupled to the air supply measurement system 1510, which includes one or more sensors, gauges, valves, and other components to control the amount of gas, such as air, being supplied to the endoscope 100 to drive the rotor 440. In some embodiments, the amount of air being supplied to the rotor 440 may be controlled using the air supply measurement system 1510. Furthermore, delivery of the air to actuate the rotor 440 may be manually controlled by the physician using the endoscope 100. In one embodiment, the physician may use a foot pedal or a hand-actuated lever to supply air to the rotor 440.

The pneumatic air exit conduit 414, however, may not be coupled to any component. As a result, air exiting from the rotor 440 may simply exit the endoscope via the pneumatic air exit conduit 414 into the atmosphere. In some embodiments, the pneumatic air exit conduit 414 may be coupled to the air supply measurement system 1510 such that the air exiting the pneumatic air exit conduit 414 is supplied back to the rotor via the pneumatic air entry conduit 412. It should be appreciated that a similar setup may be used for a hydraulically driven turbine system.

The endoscope 100 may also be coupled to the irrigation system 1530 via the irrigation fluid conduit 416. The irrigation system 1530 may include a flow meter 1534 coupled to an irrigation source 1532 for controlling the amount of fluid flowing from the irrigation source 1532 to the endoscope 100.

As described above, the endoscope 100 may also include a suction conduit 418 for removing polyps from within the patient's body. The suction conduit 418 may be coupled to the polyp removal system 1540, which may be configured to store the polyps. In various embodiments, the physician may be able to collect samples in one or more cartridges 1542 within the polyp removal system 1540 such that the removed polyps can be tested individually.

In various embodiments of the present disclosure, an endoscope, comprises a first end and a second end separated by a flexible housing, an instrument channel extending from the first end to the second end, and an endoscopic instrument comprising a debriding component and a sample retrieval conduit disposed within the instrument channel. The endoscopic instrument may further include a flexible tubing in which the sample retrieval conduit is partially disposed, the flexible tubing extending from the first end to the second end of the endoscope. The flexible tubing may also include a pneumatic air entry conduit and a fluid irrigation conduit. In various embodiments, the debriding component may include a turbine assembly and a cutting tool. In various embodiments in which the endoscope is configured to have a built in endoscopic instrument, the instrument channel may have a diameter that is larger than the instrument channels of existing endoscopes. In this way, larger portions of debrided material may be suctioned from within the patient's body without clogging the suction conduit.

In other embodiments, an endoscope may include a first end and a second end separated by a flexible housing; an instrument channel extending from the first end to the second end; and an endoscopic instrument coupled to the instrument channel at the first end of the endoscope, the endoscopic instrument comprising a debriding component and a sample retrieval conduit partially disposed within the instrument channel. In some embodiments, the endoscopic instrument may be removably attached to the endoscopic instrument.

In other embodiments of the present disclosure, an endoscopic system, includes an endoscope comprising a first end and a second end separated by a flexible housing and an instrument channel extending from the first end to the second end and an endoscopic instrument coupled to the instrument channel at the first end of the endoscope. The endoscopic instrument may include a debriding component and a flexible tubing having a length that is greater than the length of the endoscope. Moreover, the flexible tubing may include a sample retrieval conduit, an pneumatic air entry conduit, and a fluid irrigation conduit, a disposable cartridge configured to couple with the sample retrieval conduit proximal the second end of the endoscope, a pressurized air source configured to couple with the pneumatic air entry conduit proximal the second end of the endoscope, and a fluid irrigation source configured to couple with the fluid irrigation conduit proximal the second end of the endoscope. In various embodiments, the endoscope may also include at least one camera source and at least one light source. In some embodiments of the present disclosure, the pneumatic air entry conduit supplies pressurized air to a turbine assembly of the debriding component proximal the first end of the endoscope and the fluid irrigation conduit supplies irrigation fluid to the sample retrieval conduit proximal the first end of the endoscope.

FIG. 16A illustrates an exploded partial view of an endoscopic instrument 1600, which is similar to the endoscopic instrument 150 depicted in FIG. 1C in that the endoscopic instrument 1600 is configured to be inserted within an instrument channel of an endoscope, such as the endoscope 100 depicted in FIG. 1B. FIG. 16B illustrates a cross-sectional partial view of the endoscopic instrument shown in FIG. 16A. As shown in FIGS. 16A and 16B, a head portion of the endoscopic instrument 1600 can include a powered actuator 1605, a power-driven instrument head 1680 including a cutting shaft 1610 and an outer structure 1615 and a feedthrough connector 1620 coupled to a distal end of a flexible tubular member 1630. The flexible tubular member 1630 forms the tail portion of the endoscopic instrument 1600. As such, FIGS. 16A and 16B illustrate the head portion of the endoscopic instrument 1600.

The endoscopic instrument 1600 is configured to define an aspiration channel 1660 that extends from a proximal end of the flexible tubular member 1630 to a distal tip 1614 of the power-driven instrument head 1680. In some implementations, the proximal end of the flexible tubular member 1630 may be configured to fluidly couple to a vacuum source. In this way, upon the application of a suction force at the proximal end of the flexible tubular member 1630, material at or around the distal tip 1614 of the power-driven instrument head 1680 can enter the endoscopic instrument 1600 at the distal tip and flow through the aspiration channel 1660 all the way to the proximal end of the flexible tubular member 1630.

The powered actuator 1605 can be configured to drive a power-driven instrument head 1680, which includes the cutting shaft 1610 disposed within the outer structure 1615. In some implementations, the powered actuator 1605 can include a drive shaft 1608 that is mechanically coupled to the cutting shaft 1610. In some implementations, one or more coupling elements may be used to couple the drive shaft 1608 to a proximal end 1611 of the cutting shaft 1610 such that the cutting shaft 1610 is driven by the drive shaft 1608. The powered actuator 1605 can be an electrically powered actuator. In some implementations, the electrically powered actuator can include an electrical terminal 1606 configured to receive an electrical conducting wire for providing electrical current to the electrically powered actuator 1605. In some implementations, the electrically powered actuator can include an electric motor. In some implementations, the electric motor can be a micro-sized motor, such that the motor has an outer diameter of less than a few millimeters. In some implementations, the powered actuator 1605 has an outer diameter that is smaller than about 3.8 mm. In addition to having a small footprint, the powered actuator 1605 may be configured to meet certain torque and rotation speed parameters. In some implementations, the powered actuator 1605 can be configured to generate enough torque and/or rotate at sufficient speeds to be able to cut tissue from within a subject. Examples of motors that meet these requirements include micromotors made by Maxon Precision Motors, Inc., located in Fall River, Mass., USA. Other examples of electrical motors include any type of electric motors, including AC motors, DC motors, piezoelectric motors, amongst others.

The power-driven instrument head 1680 is configured to couple to the powered actuator 1605 such that the powered actuator 1605 can drive the power-driven instrument head. As described above, the proximal end 1611 of the cutting shaft 1610 can be configured to couple to the drive shaft 1608 of the powered actuator 1605. The distal end 1614 of the cutting shaft 1610 opposite the proximal end 1611 can include a cutting tip 1612. The cutting tip 1612 can include one or more sharp surfaces capable of cutting tissue. In some implementations, the cutting shaft 1610 can be hollow and can define a material entry port 1613 at or around the cutting tip 1612 through which material that is cut can enter the endoscopic instrument 1610 via the material entry port 1613. In some implementations, the proximal end 1611 of the cutting shaft 1610 can include one or more outlet holes 1614 that are sized to allow material flowing from the material entry port 1613 to exit from the cutting shaft 1610. As shown in FIGS. 16A and 16B, the outlet holes 1614 are defined within the walls of the cutting shaft 1610. In some implementations, these outlet holes 1614 can be sized such that material entering the cutting shaft 1610 via the material entry port 1613 can flow out of the cutting shaft 1610 via the outlet holes 1614. In some implementations, the portion of the cutting shaft 1610 proximal the drive shaft 1608 may be solid such that all the material that enters the cutting shaft 1610 flows out of the cutting shaft 1610 via the outlet holes 1614.

The outer structure 1615 can be hollow and configured such that the cutting shaft can be disposed within the outer structure 1615. As such, the outer structure 1615 has an inner diameter that is larger than the outer diameter of the cutting shaft 1610. In some implementations, the outer structure 1615 is sized such that the cutting shaft 1610 can rotate freely within the outer structure 1615 without touching the inner walls of the outer structure 1615. The outer structure 1615 can include an opening 1616 at a distal end 1617 of the outer structure 1615 such that when the cutting shaft 1610 is disposed within the outer structure 1615, the cutting tip 1612 and the material entry port 1613 defined in the cutting shaft 1610 is exposed. In some implementations, the outer surface of the cutting shaft 1610 and the inner surface of the outer structure 1615 can be coated with a heat-resistant coating to help reduce the generation of heat when the cutting shaft 1610 is rotating within the outer structure 1615. A proximal end of the outer structure 1615 is configured to attach to the housing that houses the powered actuator 1605.

The feedthrough connector 1620 can be positioned concentrically around the portion of the cutting shaft 1610 that defines the outlet holes 1614. In some implementations, the feedthrough connector 1620 can be hollow and configured to enclose the area around the outlet holes 1614 of the cutting shaft 1610 such that material leaving the outlet holes 1614 of the cutting shaft 1610 is contained within the feedthrough connector 1620. The feedthrough connector 1620 can include an exit port 1622, which can be configured to receive the distal end of the tubular member 1630. In this way, any material within the feedthrough connector 1620 can flow into the distal end of the flexible tubular member 1630. The feedthrough connector 1620 can serve as a fluid coupler that allows fluid communication between the cutting shaft 1610 and the tubular member 1630.

The tubular member 1630 can be configured to couple to the exit port 1622 of the feedthrough connector 1620. By way of the cutting shaft 160, the feedthrough connector 1620 and the flexible tubular member 1630, the aspiration channel 1660 extends from the material entry port 1613 of the cutting shaft 1610 to the proximal end of the tubular member 1630. In some implementations, the tubular member 1630 can be configured to couple to a vacuum source at the proximal end of the tubular member 1630. As such, when a vacuum source applies suction at the proximal end of the tubular member 1630, material can enter the aspiration channel via the material entry port 1613 of the cutting shaft 1610 and flow through the aspiration channel 1660 towards the vacuum source and out of the endoscopic instrument 1600. In this way, the aspiration channel 1660 extends from one end of the endoscopic instrument to the other end of the endoscopic instrument 1600. In some implementations, a vacuum source can be applied to the tubular member 1630 such that the material at the treatment site can be suctioned from the treatment site, through the aspiration channel 1660 and withdrawn from the endoscopic instrument 1600, while the endoscopic instrument 1600 remains disposed within the instrument channel of the endoscope and inside the subject being treated. In some implementations, one or more of the surfaces of the cutting shaft 1610, the feedthrough connector 1620 or the tubular member 1630 can be treated to improve the flow of fluid. For example, the inner surfaces of the cutting shaft 1610, the feedthrough connector 1620 or the tubular member 1630 may be coated with a superhydrophobic material to reduce the risk of material removed from within the patient from clogging the suction conduit.

Examples of various types of instrument heads that can be coupled to the powered actuator 1605 are disclosed in U.S. Pat. Nos. 4,368,734, 3,618,611, 5,217,479, 5,931,848 and U.S. Pat. Publication 2011/0087260, amongst others. In some other implementations, the instrument head can include any type of cutting tip that is capable of being driven by a powered actuator, such as the powered actuator 1650, and capable of cutting tissue into small enough pieces such that the tissue can be removed from the treatment site via the aspiration channel defined within the endoscopic instrument 1600. In some implementations, the power-driven instrument head 1680 may be configured to include a portion through which material from the treatment site can be removed. In some implementations, the circumference of the aspiration channel can be in the order of a few micrometers to a few millimeters.

In some implementations, where the powered actuator 1620 utilizes an electric current for operation, the current can be supplied via one or more conductive wires that electrically couple the powered actuator to an electrical current source. In some implementations, the electrical current source can be external to the endoscopic instrument 1600. In some implementations, the endoscopic instrument 1600 can include an energy storage component, such as a battery that is configured to supply electrical energy to the electrical actuator. In some implementations, the energy storage component can be positioned within the endoscopic instrument. In some implementations, the energy storage component or other power source may be configured to supply sufficient current to the powered actuator that cause the powered actuator to generate the desired amount of torque and/or speed to enable the cutting shaft 1610 to cut tissue material. In some implementations, the amount of torque that may be sufficient to cut tissue can be greater than or equal to about 2.5 N mm. In some implementations, the speed of rotation of the cutting shaft can be between 1000 and 5000 rpm. However, these torque ranges and speed ranges are examples and are not intended to be limiting in any manner.

The endoscopic instrument 1600 can include other components or elements, such as seals 1640 and bearings 1625, which are shown. In some implementations, the endoscopic instrument 1600 can include other components that are not shown herein but may be included in the endoscopic instrument 1600. Examples of such components can include sensors, cables, wires, as well as other components, for example, components for engaging with the inner wall of the instrument channel of an endoscope within which the endoscopic instrument can be inserted. In addition, the endoscopic instrument can include a housing that encases one or more of the powered actuator, the feedthrough connector 1620, any other components of the endoscopic instrument 1600. In some implementations, the tail portion of the endoscopic instrument 1600 can also include a flexible housing, similar to the flexible portion 165 shown in FIG. 1C, that can carry one or more flexible tubular members, such as the flexible tubular member 1630, as well as any other wires, cables or other components.

In some implementations, the endoscopic instrument can be configured to engage with the instrument channel of an endoscope in which the instrument is inserted. In some implementations, an outer surface of the head portion of the endoscopic instrument can engage with an inner wall of the instrument channel of the endoscope such that the endoscopic instrument does not experience any unnecessary or undesirable movements that may occur if endoscopic instrument is not supported by the instrument channel. In some implementations, the head portion of the body of the endoscopic instrument can include a securing mechanism that secures the head portion of the body to the inner wall of the instrument channel. In some implementations, the securing mechanism can include deploying a frictional element that engages with the inner wall. The frictional element can be a seal, an o-ring, a clip, amongst others.

FIG. 16C illustrates a schematic view of an engagement assembly of an example endoscopic instrument. FIG. 16D shows a cut-open view of the engagement assembly when the engagement assembly is disengaged. FIG. 16E shows a cut-open view of the engagement assembly when the engagement assembly is configured to engage with an instrument channel of an endoscope. As shown in FIGS. 16C and 16D, the engagement assembly 1650 includes a housing portion 1652 that defines a cylindrical groove 1654 around an outer surface 1656 of the housing portion. The groove 1654 is sized such that a compliant seal component 1670 can be partially seated within the groove 1654. A cylindrical actuation member 1660 is configured to encompass the housing portion 1652. The cylindrical actuation member 1660 can slidably move along the length of the housing portion 1652. The cylindrical actuation member 1660 is configured to engage the securing member 1670 by pressing on the surface of the securing member 1670. The actuation member 1660 can apply a force on the securing member 1670 causing the securing member 1670 to deform such that the securing member 1670 becomes flatter and wider. The securing member 1670 is configured such that when the securing member 1670 widens, the outer surface of the securing member 1670 can engage with an inner surface of the instrument channel of an endoscope in which the endoscopic instrument is inserted. In this way, when the cylindrical actuation member 1660 is actuated, the endoscopic instrument 1600 can engage with the instrument channel thereby preventing the endoscopic instrument 1600 from moving relative to the instrument channel. This can help provide stability to the operator while treating the subject. In some implementations, more than one engagement assembly 1650 can be positioned along various portions of the endoscopic instrument 1600.

FIG. 17A illustrates an exploded view of an example endoscopic instrument 1700 according to embodiments of the present disclosure. FIG. 17B illustrates a cross-sectional view of the endoscopic instrument 1700. The endoscopic instrument 1700, similar to the endoscopic instrument 1600 shown in FIGS. 16A and 16B, can also be configured to be inserted within an instrument channel of an endoscope, such as the endoscope 100 depicted in FIG. 1B. The endoscopic instrument 1700, however, differs from the endoscopic instrument 1600 in that the endoscopic instrument 1700 defines an aspiration channel 1760 that extends through a powered actuator 1705. In this way, material entering a material entry port 1713 of the endoscopic instrument 1700 can flow through the endoscopic instrument 1700 and out of the endoscopic instrument in a straight line.

As shown in FIGS. 17A and 17B, the endoscopic instrument 1700 is similar to the endoscopic instrument 1600 except that the endoscopic instrument includes a different powered actuator 1705, a different cutting shaft 1710 and a different feedthrough connector 1720. The powered actuator 1705 is similar to the powered actuator 1605 shown in FIG. 16A but differs in that the powered actuator 1705 includes a drive shaft 1708 that is hollow and extends through the length of the powered actuator 1705. Since some of the components are different, the manner in which the endoscopic instrument is assembled is also different.

In some implementations, the powered actuator 1605 can be any actuator capable of having a hollow shaft that extends through the length of the motor. The distal end 1708 a of the drive shaft 1708 includes a first opening and is coupled to the proximal end 1711 of the cutting shaft 1705. Unlike the cutting shaft 1610, the cutting shaft 1710 includes a fluid outlet hole 1714 at the bottom of the cutting shaft 1710. As a result, the entire length of the cutting shaft 1710 is hollow. The proximal end 1708 b of the drive shaft 1708 is configured to couple to the feedthrough connector 1720, which differs from the feedthrough connector 1620 in that the feedthrough connector 1720 includes a hollow bore 1722 defining a channel in line with the proximal end of the drive shaft such that the drive shaft 1708 and the hollow bore 1722 are fluidly coupled. The hollow bore 1722 can be configured to couple to the flexible tubular member 1730, which like the flexible tubular member 1630, extends from the feedthrough connector at a distal end to a proximal end that is configured to couple to a vacuum source.

As shown in FIGS. 17A and 17B, the drive shaft 1708 can be hollow, such that the drive shaft 1708 defines a first opening at a distal end 1708 a and a second opening at a proximal end 1708 b of the drive shaft 1708. The cutting shaft 1710 is also hollow and defines an opening 1714 at the bottom end 1710 a of the cutting shaft 1710. The distal end 1708 a of the drive shaft 1708 is configured to couple to the bottom end 1710 a of the cutting shaft 1710 such that the first opening of the drive shaft 1708 is aligned with the opening at the bottom end 1710 a of the cutting shaft 1710. In this way, the drive shaft 1708 can be fluidly coupled to the cutting shaft 1710. A distal end 1710 b of the cutting shaft 1710 includes a cutting tip 1712 and the material entry port 1713.

The proximal end 1708 a of the drive shaft 1708 is fluidly coupled to a distal end of the flexible tubular member 1730 via the feedthrough connector 1720. In some implementations, the feedthrough connector 1720 couples the drive shaft and the flexible tubular member such that the flexible tubular member does not rotate with the drive shaft. The proximal end of the flexible tubular member can be configured to couple to a vacuum source.

As shown in FIG. 17B, the endoscopic instrument 1700 defines an aspiration channel 1760 that extends from the material entry port 1713 through the cutting shaft, the drive shaft, the feedthrough connector 1720 to the second end of the flexible tubular member 1730. In this way, material that enters the material entry port 1713 can flow through the length of the endoscopic instrument and exit from the endoscopic instrument at the second end of the endoscopic instrument.

Other components of the endoscopic instrument 1700 are similar to those shown in the endoscopic instrument 1600 depicted in FIGS. 16A and 16B. For example, the outer structure 1715, the encoding component 1606, the seals and the bearings may be substantially similar to the outer structure 1615, the encoding component 1606, the seals 1640 and the bearings 1625 depicted in FIG. 16. Other components, some of which are shown, may be included to construct the endoscopic instrument and for proper functioning of the instrument.

FIG. 18A illustrates an exploded view of an example endoscopic instrument 1800 according to embodiments of the present disclosure. FIG. 18B illustrates a cross-sectional view of the endoscopic instrument 1800. The endoscopic instrument 1800, similar to the endoscopic instrument 1700 shown in FIGS. 17A and 17B, can also be configured to be inserted within an instrument channel of an endoscope, such as the endoscope 100 depicted in FIG. 1B. The endoscopic instrument 1800, however, differs from the endoscopic instrument 1700 in that the endoscopic instrument 1800 includes a pneumatic or hydraulically powered actuator 1805.

In some implementations, the powered actuator 1802 includes a tesla turbine that includes a tesla rotor 1805, a housing 1806 and a connector 1830 that along with the housing 1806 encases the tesla rotor 1805. The tesla rotor 1805 can include a plurality of disks 1807 spaced apart and sized such that the tesla rotor 1805 fits within the housing. In some implementations, the tesla rotor can include between 7 and 13 disks having a diameter between about 2.5 mm and 3.5 mm and thicknesses between 0.5 mm to 1.5 mm. In some implementations, the disks are separated by gaps that range from 0.2 mm to 1 mm. The tesla turbine 1802 also can include a hollow drive shaft 1808 that extends along a center of the tesla rotor 1805. In some implementations, a distal end 1808 a of the drive shaft 1808 is configured to be coupled to a cutting shaft 1810 such that the cutting shaft 1810 is driven by the tesla rotor. That is, in some implementations, the cutting shaft 1810 rotates as the drive shaft 1808 of the tesla rotor 1805 is rotating. In some implementations, the cutting shaft 1810 can include outlet holes similar to the cutting shaft 1610 shown in FIG. 16A. In some such implementations, the feedthrough connector fluidly couples the cutting shaft and the flexible portion similar to the feedthrough connector 1630 shown in FIG. 16A.

The connector 1830 of the tesla turbine 1802 can include at least one fluid inlet port 1832 and at least one fluid outlet port 1834. In some implementations, the fluid inlet port 1832 and the fluid outlet port 1834 are configured such that fluid can enter the tesla turbine 1802 via the fluid inlet port 1832, cause the tesla rotor 1805 to rotate, and exit the tesla turbine 1802 via the fluid outlet port 1834. In some implementations, the fluid inlet port 1832 is fluidly coupled to a fluid inlet tubular member 1842 configured to supply fluid to the tesla rotor via the fluid inlet port 1832. The fluid outlet port 1834 is fluidly coupled to a fluid outlet tubular member 1844 and configured to remove the fluid supplied to the tesla turbine 1802. The amount of fluid being supplied and removed from the tesla turbine 1802 can be configured such that the tesla rotor 1805 can generate sufficient torque, while rotating at a sufficient speed to cause the cutting shaft 1810 to cut tissue at a treatment site. In some implementations, the fluid can be air or any other suitable gas. In some other implementations, the fluid can be any suitable liquid, such as water. Additional details related to how fluid can be supplied or removed from pneumatic or hydraulic actuators, such as the tesla turbine 1802 has been described above with respect to FIGS. 4A-15.

The connector 1830 also includes a suction port 1836 that is configured to couple to an opening defined at a proximal end 1808 b of the hollow drive shaft 1808. The suction port 1836 is further configured to couple to a distal end of a flexible tubular member 1846, similar to the flexible tubular member 1730 shown in FIG. 17A, which is configured to couple to a vacuum source at a proximal end. In some implementations, a flexible tubular housing can include one or more of the fluid inlet tubular member 184, fluid outlet tubular member 1844 and the flexible tubular member 1846. In some implementations, the flexible tubular housing can include other tubular members and components that extend from the head portion of the endoscopic instrument to the proximal end of the tail portion of the endoscopic instrument 1800.

The cutting shaft 1810 and an outer structure 1815 are similar to the cutting shaft 1710 and the outer structure 1715 of the endoscopic instrument 1700 depicted in FIG. 17A. The cutting shaft 1810 is hollow and defines an opening at a proximal end 1810 b of the cutting shaft 1810. The proximal end 1810 b of the cutting shaft 1810 is configured to couple to a distal end 1808 a of the drive shaft 1808 such that an opening at the distal end 1808 a of the drive shaft 1808 is aligned with the opening defined at the proximal end 1808 b of the cutting shaft 1810. In this way, the drive shaft 1808 can be fluidly coupled to the cutting shaft 1810. A distal end 1810 b of the cutting shaft 1810 includes a cutting tip 1812 and a material entry port 1813 similar to the cutting shafts 1610 and 1710 shown in FIGS. 16A and 17A.

In some implementations, an irrigation opening 1852 can be formed in the housing 1806. The irrigation opening 1852 is configured to be fluidly coupled to the aspiration channel 1860. In some such implementations, the irrigation opening 1852 is configured to be fluidly coupled to a gap (not clearly visible) that separates the walls of outer structure 1815 and the cutting shaft 1810. In this way, fluid supplied to the tesla turbine 1802 can escape via the irrigation opening 1852 in to the gap. The fluid can flow towards the material entry port 1813 of the cutting shaft 1810, through which the fluid can enter the aspiration channel 1860. In some implementations, since the aspiration channel 1860 is fluidly coupled to a vacuum source, the fluid from the tesla turbine 1802 can be directed to flow through the aspiration channel 1860 as irrigation fluid along with any other material near the material entry port 1813. In this way, the irrigation fluid can irrigate the aspiration channel 1860 to reduce the risk of blockages.

In addition, as the irrigation fluid flows in the gap separating the outer structure 1815 and the cutting shaft 1810, the irrigation fluid can serve to reduce the generation of heat. In some implementations, one or both of the cutting shaft 1810 and the outer structure 1815 can be coated with a heat-resistant layer to prevent the cutting shaft and the outer structure from getting hot. In some implementations, one or both of the cutting shaft 1810 and the outer structure 1815 can be surrounded by a heat-resistant sleeve to prevent the cutting shaft 1810 and the outer structure 1815 from getting hot.

In some implementations, other types of hydraulically or pneumatically powered actuators can be utilized in place of the tesla turbine. In some implementations, a multi-vane rotor can be used. In some such implementations, the powered actuator can be configured to be fluidly coupled to a fluid inlet tubular member and a fluid outlet tubular member similar to the tubular members 1842 and 1844 shown in FIG. 18B.

As described above with respect to the endoscopic instruments 1600, 1700 and 1800 depicted in FIGS. 16A, 17A and 18A, an endoscopic instrument is configured to meet certain size requirements. In particular, the endoscopic instrument can be long enough such that when the endoscopic instrument is completely inserted into the endoscope, the power-driven instrument head can extend beyond the face of the endoscope at one end such that the cutting tip is exposed, while the tail portion of the endoscopic instrument can extend out of the other end of the endoscope such that the tail portion can be coupled to a vacuum source. As such, in some implementations, the endoscopic instrument may be configured to be longer than the endoscopes in to which the endoscopic instrument will be inserted. Further, since endoscopes have instrument channels that have different diameters, the endoscopic instrument may also be configured to have an outer diameter that is sufficiently small such that the endoscopic instrument can be inserted into the instrument channel of the endoscope in to which the endoscopic instrument will be inserted.

Some endoscopes, such as colonoscopes, can have instrument channels that have an inner diameter that can be as small as a few millimeters. In some implementations, the outer diameter of the endoscopic instrument can be less than about 3.2 mm. As such, powered actuators that are part of the endoscopic instrument may be configured to have an outer diameter than is less than the outer diameter of the endoscopic instrument. At the same time, the powered actuators may be configured to be able to generate sufficient amounts of torque, while rotating at speeds sufficient to cut tissue at a treatment site within a subject.

In some other implementations, the endoscopic instrument can be configured such that a powered actuator is not housed within the endoscopic instrument at all or at least within a portion of the endoscopic instrument that can be inserted within the instrument channel of an endoscope. Rather, the endoscopic instrument includes a flexible cable that is configured to couple a power-driven instrument head of the endoscopic instrument to a powered actuator that is located outside of the endoscope.

FIG. 19A illustrates an example endoscopic instrument 1900 that is coupled to a powered actuation and vacuum system 1980. The endoscopic instrument includes a head portion 1902 and a tail portion. The tail portion includes the flexible cable 1920, which can provide torque to the head portion 1902. The powered actuation and vacuum system 1980 includes a powered actuator 1925, a coupler 1935 and a vacuum tubing 1930 configured to couple to the couple 1935 at a first end 1932 and couple to a vacuum source at a second end 1934. In some implementations, the flexible cable 1920 can be hollow and configured to carry fluid from the head portion 1902 to the coupler 1935.

FIG. 19B illustrates a cross-section view of the powered actuation and vacuum system 1980 of FIG. 19A. The powered actuator 1925 includes a drive shaft 1926 that is mechanically coupled to a proximal end 1922 of the flexible cable 1920. In some implementations, the drive shaft 1926 and the flexible cable 1920 are mechanically coupled via the coupler 1935. The coupler 1935 includes a vacuum port 1936 to which a first end 1932 of the vacuum tubing 1930 can be fluidly coupled. The coupler 1935 can be enclosed such that the vacuum tubing 1930 and the flexible cable are fluidly coupled. In this way, suction applied in the vacuum tubing 1930 can be applied all the way through the flexible cable 1920 to the head portion 1902 of the endoscopic instrument 1900. Further, any material that is in the flexible cable 1920 can flow through the flexible cable to the vacuum tubing 1930 via the coupler 1935. In some implementations, the coupling between the flexible cable and the vacuum tubing can occur within the head portion 1902. In such implementations, the coupler 1935 may be configured to be small enough to be positioned within the head portion 1902.

FIG. 19C illustrates an exploded view of an example head portion of the endoscopic instrument 1900 shown in FIG. 19A. The head portion includes a housing cap 1952, a collet 1954, a cutting shaft 1956, a shaft coupler 1958 and a head portion housing 1960. In some implementations, the collet 1954 is slightly tapered towards a distal end such that the collet 1954 can couple with the cutting shaft 1956 that is disposed within the collet 1954. The shaft coupler 1958 is configured to couple the cutting shaft to the distal end of the flexible cable 1920. The head portion 1960 and the housing cap 1952 are configured to house the shaft coupler 1958.

FIG. 19D illustrates a cut-open view of a portion of the endoscopic instrument 1900 having an engagement assembly. In some implementations, the head portion housing 1960 can include an engagement assembly for engaging with the inner walls of an instrument channel. The engagement assembly can be similar to the engagement assembly 1650 shown in FIG. 16C. In some implementations, the engagement assembly can be actuated via a vacuum source. FIG. 19E shows a cut-open view of the engagement assembly shown in FIG. 19D in a disengaged position. FIG. 19F shows a cut-open view of the engagement assembly shown in FIG. 19D in an engaged position.

The engagement assembly can include a pair of vacuum actuated members 1962 that are configured to rotate between an extended position in which the members 1962 are extended outwardly to engage with a wall of the instrument channel 1990 and a retracted position in which the members 1962 are positioned such that they lie substantially parallel to the walls of the instrument channel 1990. The grooves 1964 are fluidly coupled to an aspiration channel 1970 defined within the flexible cable 1920. In some implementations, fluid channels 1966 fluidly couple the grooves 1964 to the aspiration channel 1970. When a vacuum source is applied to the aspiration channel 1970, a suction force is applied to the members 1962 causing them to move from a retracted position (as shown in FIG. 19E) to an extended position (as shown in FIG. 19F). In some implementations, the engagement assembly can also include an outer ring supported by the vacuum actuated members 1964. The outer ring 1966 can be configured to assist in guiding the endoscopic instrument through the instrument channel of the endoscope. In particular, the outer ring can prevent the endoscopic instrument from tilting to one side causing the power-driven instrument head from jarring against the instrument channel.

The endoscopic instrument 1900 is similar to the endoscopic instruments 1600, 1700 and 1800 depicted in FIGS. 16A-18A respectively but differs from them in that the endoscopic instrument 1900 does not include a powered actuator within the head portion 1902 of the endoscopic instrument 1900. Instead, the endoscopic instrument 1900 includes a flexible cable 1920 for providing torque to a power-driven instrument head 1904 of the endoscopic instrument 1900. In some implementations, the power-driven instrument head 1904 can be similar to the power-driven instrument heads depicted in FIGS. 16A-18A. In some implementations, the flexible cable 1920 can be hollow such that fluid can flow through the flexible cable 1920. In some such implementations, a proximal end 1922 of the flexible cable 1920 can be configured to couple to a vacuum source, while a distal end 1921 of the flexible cable 1920 can be coupled to the power-driven instrument head 1904. In this way, fluid that enters a material entry port 1907 can flow through the power-driven instrument head 1904 and into the flexible cable 1920, from which the fluid can flow through the flexible cable 1920 and be removed from the endoscopic instrument 1900 at the proximal end 1922 of the flexible cable 1920.

In some implementations, a flexible cable, such as the flexible cable 1920 can replace a powered actuator and drive shaft that are housed within an endoscopic instrument. For example, the endoscopic instruments 1600, 1700 and 1800 depicted in FIGS. 16A, 17A and 18A can be configured to utilize a flexible cable that is coupled to a cutting shaft of a power-driven instrument head at a distal end and coupled to a powered actuator located outside the endoscopic instrument at a proximal end. The powered actuator located outside the endoscopic instrument may be significantly larger than the powered actuators 1605, 1705 or 1805. As the powered actuator is actuated, torque generated by the powered actuator can be translated from the powered actuator to the power-driven instrument head via the flexible cable. The flexible cable 1920 is configured to translate torque from the powered actuator to the cutting shaft. In some implementations, the flexible cable 1920 is or includes a fine coil with multiple threads and multiple layers, which can transmit the rotation of one end of the flexible cable to an opposite end of the flexible cable. The flexibility of the cable allows the coil to maintain performance even in sections of the coil that are bent. Examples of the flexible cable 1920 include torque coils made by ASAHI INTECC USA, INC located in Santa Ana, Calif., USA. In some implementations, the flexible cable 1920 can be surrounded by a sheath to avoid frictional contact between the outer surface of the flexible cable and other surfaces. In some implementations, the flexible cable 1920 can be coated with Polytetrafluoroethylene (PFTE) to reduce frictional contact between the outer surface of the flexible cable and other surfaces.

FIG. 20 is a conceptual system architecture diagram illustrating various components for operating the endoscopic instrument according to embodiments of the present disclosure. The endoscopic system 2000 includes an endoscope 100 fitted with an endoscopic instrument 2002 that includes a flexible tail portion 2004. The endoscopic instrument can, for example, be the endoscopic instrument 220, 1600, 1700, 1800 or 1900 shown in FIGS. 4A-14, 16A, 17A, 18A and 19A. The system also includes an endoscope control unit 2005 that controls the operation of the endoscope 100 and an instrument control unit 2010 that controls the operation of the endoscopic instrument 2002.

In addition, the endoscopic instrument also includes a vacuum source 1990, a sample collection unit 2030 and a tissue sensing module 2040. The vacuum source 1990 is configured to fluidly couple to a flexible tubular member that forms a portion of the aspiration channel. In this way, material that flows from the endoscopic instrument through the aspiration channel towards the vacuum source 1990 can get collected at 2030 sample collection unit. The tissue sensing module can be communicatively coupled to a tissue sensor disposed at a distal tip of the endoscopic instrument 2000. In some such implementations, the tissue sensing module can also be configured to be communicatively coupled to the instrument control unit 2010 such that the tissue sensing module can send one or more signals instructing the control unit 2010 to stop the actuation of the powered actuator.

In some implementations in which the powered actuator is electrically actuated and disposed within the endoscopic instrument, the powered actuator can be electrically coupled to the instrument control unit 2010. In some such implementations, the powered actuator is coupled to the control unit via one or more electric cables. In some implementations, the powered actuator may be battery operated in which case, the tubing may include cables extending from the control unit to the powered actuator or the battery for actuating the powered actuator.

In some implementations in which the power-driven instrument head is coupled to a flexible torque coil that couples the power-driven instrument head to a powered actuator that resides outside of the endoscope, the powered actuator can be a part of the instrument control unit.

In various embodiments of the present disclosure, an endoscope, comprises a first end and a second end separated by a flexible housing, an instrument channel extending from the first end to the second end, and an endoscopic instrument comprising a debriding component and a sample retrieval conduit disposed within the instrument channel. The endoscopic instrument may further include a flexible tubing in which the sample retrieval conduit is partially disposed, the flexible tubing extending from the first end to the second end of the endoscope. The flexible tubing may also include a pneumatic air entry conduit and a fluid irrigation conduit. In various embodiments, the debriding component may include a turbine assembly and a cutting tool. In various embodiments in which the endoscope is configured to have a built in endoscopic instrument, the instrument channel may have a diameter that is larger than the instrument channels of existing endoscopes. In this way, larger portions of debrided material may be suctioned from within the patient's body without clogging the suction conduit.

In other embodiments, an endoscope may include a first end and a second end separated by a flexible housing; an instrument channel extending from the first end to the second end; and an endoscopic instrument coupled to the instrument channel at the first end of the endoscope, the endoscopic instrument comprising a debriding component and a sample retrieval conduit partially disposed within the instrument channel. In some embodiments, the endoscopic instrument may be removably attached to the endoscopic instrument.

In other embodiments of the present disclosure, an endoscopic system, includes an endoscope comprising a first end and a second end separated by a flexible housing and an instrument channel extending from the first end to the second end and an endoscopic instrument coupled to the instrument channel at the first end of the endoscope. The endoscopic instrument may include a debriding component and a flexible tubing having a length that is greater than the length of the endoscope. Moreover, the flexible tubing may include a sample retrieval conduit, an pneumatic air entry conduit, and a fluid irrigation conduit, a disposable cartridge configured to couple with the sample retrieval conduit proximal the second end of the endoscope, a pressurized air source configured to couple with the pneumatic air entry conduit proximal the second end of the endoscope, and a fluid irrigation source configured to couple with the fluid irrigation conduit proximal the second end of the endoscope. In various embodiments, the endoscope may also include at least one camera source and at least one light source. In some embodiments of the present disclosure, the pneumatic air entry conduit supplies pressurized air to a turbine assembly of the debriding component proximal the first end of the endoscope and the fluid irrigation conduit supplies irrigation fluid to the sample retrieval conduit proximal the first end of the endoscope.

As described above with respect to FIGS. 19A-19C, the endoscopic tool can include a flexible cable that can be configured to be driven by a powered actuator that resides outside the endoscopic tool itself. The flexible cable can be a torque coil or rope.

FIGS. 21AA-21F illustrate aspects of an endoscopic assembly. In particular, Figures FIGS. 21AA-21F illustrate various views of an endoscopic tool 2110 coupled to a powered actuator 2120 encased in a housing 2150. As shown in FIG. 21, the powered actuator 2120 can be a motor that is operatively coupled to a flexible cable via a pulley system. A casing 2150 including one or more structures, such as a base plate 2152, one or more side plates 2154 and a top plate 2156 can encase the motor 2120. A coupling component 2130 can be configured to couple the flexible cable 2114 to the motor 2120, while providing a suction mechanism to remove any fluids passing through the endoscopic tool 2110. The coupling component 2130 can include a suction port 2170 through which fluid within the endoscopic tool 2110 can be removed and collected. In FIG. 21B, a pair of pulleys 2160 and 2162 coupled to a timing belt 2164 are configured such that rotational energy from the motor is transferred to one end of the flexible cable 2114. The other end of the flexible cable 2114 can be coupled to a cutting member 2112. Additional details regarding the flexible cable 2114 are described herein with respect to FIGS. 22A-22H.

FIGS. 22A-22H show various implementations of example flexible cables. In some implementations, the flexible cable can be made of three separate threads or wires. An inner wire can have a left-hand wound, a middle wire can have a right-hand wound and the outer wire can have a left-hand wound. In some implementations, the inner wire can have a right-hand wound, a middle wire can have a left-hand wound and the outer wire can have a right-hand wound. In some implementations, the flexible cable can be made of two separate threads or wires. In some such implementations, the inner wire can have a left-hand wound and the outer wire can have a right-hand wound. In some other implementations, the inner wire can have a right-hand wound and the outer wire can have a left-hand wound. In some implementations, the wirerope strands can be twisted in either Z-lay or S-lay. Examples of flexible cables include wireropes and torque coils manufactured by ASAHI INTECC. In some implementations, the outer diameter of the torque rope or coil is limited by the size of the working channel of the endoscope with which the endoscopic tool will be used. Other size considerations that need to be taken into account include providing enough space for the aspiration channel, irrigation channel, amongst others. In some implementations, the outer diameter of the torque coil or torque rope can range between 0.1 mm and 4 mm. In some implementations, the torque coil or rope can have an outer diameter of 0.5 mm to 2.0 mm.

Referring back to FIG. 21D, a cross-sectional view of the coupling component 2130 is shown. The coupling component 2130 couples one end of the endoscopic tool to the powered actuator 2120 via the pulleys 2160 and 2162 and to the suction port 2170. The coupling component includes a collection chamber 2181, which is where fluid within the aspirating tube 2118 of the endoscopic tool 2110 can be collected before being suctioned out from the coupling component 2130. The coupling component includes a collection chamber 2181 can also include a drive shaft 2186 that is configured to engage with the pulley 2162. The flexible cable or torque rope 2114 can be coupled to one end of the drive shaft 2186. An opposite end of the drive shaft 2186 is coupled to the pulley 2162, such that the drive shaft is operatively coupled with the motor 2120. In this way, as the motor rotates, the pulleys and the timing belt 2164 are configured to rotate the drive shaft 2186, and in turn, the torque rope 2114. FIGS. 24A-24C illustrate various aspects of the drive shaft of the coupling component 2130. As shown in FIGS. 24A-24C, the drive shaft 2186 can be configured to receive one end of the flexible cable via an opening 2406. A pair of holes 2402 a and 2402 b can be configured to receive set screws or other securing members for securing the flexible cable to the drive shaft 2186.

The coupling component 2130 also includes a housing component 2500 that couples a flexible portion of the endoscopic tool to the suction port 2170 via an opening 2502. FIG. 25 illustrates an example housing component 2500.

FIGS. 26A-26E show an example sleeve bearing.

FIGS. 27A-27C show an example base plate 2152 that forms a portion of the casing. FIGS. 28A-28D show an example side plate that forms a portion of the casing. The side plate can also serve as a feedthrough mount.

In some implementations, the coupling component is a part of the endoscopic tool. In some implementations, the coupling component is coupled to a flexible portion of the endoscopic tool via a compression fitting component 2182.

The flexible portion of the endoscopic tool includes an outer tubing, which includes an aspiration tube 2118, the torque rope 2114 and a sheath 2116 that surrounds the outer circumference of the torque rope 2114. The sheath can help reduce friction or the formation of kinks. The aspiration tube 2118 is configured to couple to a cutting tool 2190 such that material that enters into the cutting tool 2190 via an opening 2193 can pass through the length of the endoscopic tool 2110 via the aspiration tube 2118.

As shown in FIGS. 21E-21F, the torque rope is configured to be coupled to an inner cannula 2192 that forms a portion of the cutting tool. The inner cannula 2192 can be surrounded by or disposed within the outer cannula 2191. The opening 2193 is formed within the outer cannula 2191 at one end of the cutting tool 2190. Details of the cutting tool 2190 have been provided herein. Figures FIGS. 23AA-23BB show an example implementation of a cutting tool. The cutting tool can be any type of cutting tool used in existing medical devices. The cutting tool shown in Figures FIGS. 23AA-23BB are shown only for the sake of example and the present disclosure is not intended to be limited to such sizes, shapes, or dimension. Commercially available cutting tools can be used. In some implementations, the cutting tools can be modified in length. In some implementations, the inner cannula can be bonded to the ferrule, while the outer cannula can be coupled to the outer aspirating tube. In some implementations, the connection between the outer cannula and the aspiration channel may be sealed to prevent material from leaking through the connection.

In some implementations, the torque rope 2114 is coupled to the inner cannula 2192 via a ferrule 2194. The ferrule can be a component that couples the torque rope to the inner cannula such that rotational energy within the torque rope is transferred to the inner cannula. Additional details regarding the shape, size and dimensions of the ferrule are shown in FIGS. 29AA-29EE. Depending on the size of the torque rope or flexible cable used in the endoscopic tool 2110, the shape and size of the ferrule may vary. Further, the ferrules shown in FIGS. 29A-29E are merely shown for the sake of example and are not intended to be limited to the particular size, shape, or dimensions shown in the Figures. In some implementations, the ends of the torque rope can be inserted into and bonded to short lengths of hypodermic tubing. Doing so can make it easier to attach the ferrule to the distal end, and to clamp onto on the proximal end (towards the drive shaft). In some implementations, a graphite filled cyanoacrylate, such as loctite black max, can be used. Other similar types of materials can also be used instead.

FIGS. 30AA-30C illustrate aspects of an endoscopic assembly in which the tip is press-fit. In some implementations, the flexible portion of the endoscopic tool can include a balloon structure that can be deployed such that the balloon structure can engage with the inner walls of the endoscope. The balloon structure can be coupled to an air supply line 3006 that is coupled to an air supply source, such that when air is supplied, the balloon can expand and engage with the inner wall of the endoscope. In some implementations, the balloon structure can expand asymmetrically, as shown in FIG. 30AA-30AB. In some implementations, the air supply source can be actuated via a foot pedal. An irrigation line 3002 can be configured to supply an irrigation fluid. The irrigation fluid can flow towards the cutting tool, where the irrigation fluid can then flow through the suction channels 3004. The irrigation fluid can prevent the suction channels from blockages. As shown in FIG. 30C, the flexible cable or torque rope can be press fit into a button at one end of the cutting tool.

FIGS. 31AA-31AB and 31B-31C illustrate aspects of an endoscopic assembly in which the tip is press-fit. In some implementations, the flexible portion of the endoscopic tool can include a balloon structure that can be deployed such that the balloon structure can engage with the inner walls of the endoscope. The balloon structure can be coupled to an air supply source such that when air is supplied, the balloon can expand and engage with the inner wall of the endoscope. In some implementations, the balloon structure can expand symmetrically, as shown in FIGS. 31AA and 31AB. An irrigation line can be configured to supply an irrigation fluid. The irrigation fluid can flow towards the cutting tool, where the irrigation fluid can then flow through the suction channels. The irrigation fluid can prevent the suction channels from blockages. As shown in FIG. 31C, the flexible cable or torque rope can be welded to one end of the cutting tool.

FIG. 32 shows a top view of an example flexible portion of an endoscopic tool. In some implementations, the flexible portion shown in FIG. 32 can be used with the implementations shown in FIGS. 30AA-30C and 31AA-31AB and 31B-31C. The flexible portion 3202 includes a center channel 3204 through which the flexible cable passes through. The flexible portion 3202 also includes two aspiration channels 3406 a and 3406 b, an irrigation channel 3408 and an air supply channel 3410.

In some implementations, the operating speed of the torque rope can vary. In some example implementations, the torque rope can have an operating speed within the range of 0.5 k RPM to 20 k RPM. In some implementations, the torque rope can have an operating speed within the range of 1 k RPM and 4 k RPM. In some implementations, the operating speed of the torque rope can vary. In some example implementations, the torque rope can operate with a torque of 5 to 100 mN*m (milliNewton Meters). In some implementations, the torque rope can operate with a torque of 20 to 50 mN*m (milliNewton Meters). However, it should be appreciated by those skilled in the art that the torque and running speed of the flexible cable can be altered based on the performance of the endoscopic tool. In some implementations, various factors contribute to the performance of the endoscopic tool, including the amount of suction, the type of cutter, the size of the opening in the cutter, amongst others. As such, the torque and running speed at which to operate the flexible cable can be dependent on a plurality of factors.

FIG. 33 is a cross-sectional view of an example cutting assembly of an endoscopic tool using a torque rope. The cutting assembly 3300 includes an outer cannula 3302, an inner cannula 3304 including an inner cutter 3306 disposed within the outer cannula 3302, a PTFE bearing 3308, a semi-compliant balloon 3310, and a multilumen extrusion 3312. A torque rope 3314 can be coupled to the inner cutter 3306. The diameter of the outer cannula can be between 0.05 inches to a size suitable to pass through an instrument channel of an endoscope.

FIGS. 35AA-35AC show are cross-sectional views of different configurations of the flexible portion region of one implementation of an endoscopic tool described herein. The flexible portion region can include an aspiration lumen 3402, an inflation lumen 3404, a lavage or irrigation lumen 3406 and a torque rope.

FIG. 35 shows various views of portions of an endoscopic tool. The endoscopic tool can include an outer cannula 1, an inner cutter 2, an inner cannula 3, a torque rope 4, a trilumen extrusion 5, a balloon 6, a PTFE washer 7, two sidearms 8, a proximal plug 9, an PTFE gasket 10 and a gasket cap 11.

FIG. 36 shows a cross-sectional view of the flexible portion region of one implementation of an endoscopic tool described herein. The flexible portion region can include an outer inflation jacket 3602, an outer coil 3604, a torque coil 3606, a multi-lumen extrusion 3608 disposed within the torque coil. The multi-lumen extrusion 3608 can include a lavage lumen 3610 and an aspiration lumen 3612.

FIG. 37 shows a cross-section view of one implementation of the endoscopic tool described herein. The endoscopic tool includes an outer cannula 3702, an inner cutter 3704, an inner torque coil 3706, an outer coil 3708, an outer inflation jacket and balloon 3710, and a multi-lumen extrusion 3712. A gear 3714, such as a worm gear can engage with the torque coil to drive the inner cutter.

FIGS. 38A and 38B show various views of a distal portion of one implementation of an endoscopic tool described herein. The endoscopic tool includes an outer cutter 3802 that defines an opening 3804. The endoscopic tool also includes an inner cutter 3806 disposed within the outer cutter. The inner cutter is coupled to a torque coil 3808. The torque coil is disposed within a PET heat shrink 3810 or other type of tubing. The outer cutter is coupled to a braided shaft 3812 to allow the outer cutter 3802 to rotate relative to the inner cutter 3806.

FIGS. 39A and 39B show cross-sectional views of the distal portion of the endoscopic tool shown in FIGS. 38A and 38B along the sections B-B and sections C-C.

In some implementations, an endoscopic instrument insertable within a single instrument channel of an endoscope can include a power driven instrument head or cutting assembly that is configured to resect material at a site within a subject. The cutting assembly includes an outer cannula and an inner cannula disposed within the outer cannula. The outer cannula defines an opening through which material to be resected enters the cutting assembly. The endoscopic instrument also includes a flexible outer tubing coupled to the outer cannula and configured to cause the outer cannula to rotate relative to the inner cannula. The flexible outer tubing can have an outer diameter that is smaller than the instrument channel in which the endoscopic instrument is insertable. The endoscopic instrument also includes a flexible torque coil having a portion disposed within the flexible outer tubing. The flexible torque coil having a distal end coupled to the inner cannula. The flexible torque coil is configured to cause the inner cannula to rotate relative to the outer cannula. The endoscopic instrument also includes a proximal connector coupled to a proximal end of the flexible torque coil and configured to engage with a drive assembly that is configured to cause the proximal connector, the flexible torque coil and the inner cannula to rotate upon actuation. The endoscopic instrument also includes an aspiration channel having an aspiration port configured to engage with a vacuum source. The aspiration channel is partially defined by an inner wall of the flexible torque coil and an inner wall of the inner cannula and extends from an opening defined in the inner cannula to the aspiration port. The endoscopic instrument also includes an irrigation channel having a first portion defined between an outer wall of the flexible torque coil and an inner wall of the flexible outer tubing and configured to carry irrigation fluid to the aspiration channel.

In some implementations, the proximal connector is hollow and an inner wall of the proximal connector defines a portion of the aspiration channel. In some implementations, the proximal connector is a rigid cylindrical structure and is configured to be positioned within a drive receptacle of the drive assembly. The proximal connector can include a coupler configured to engage with the drive assembly and a tensioning spring configured to bias the inner cannula towards a distal end of the outer cannula. In some implementations, the tensioning spring is sized and biased such that the tensioning spring causes a cutting portion of the inner cannula to be positioned adjacent to the opening of the outer cannula. In some implementations, the proximal connector is rotationally and fluidly coupled to the flexible torque coil. In some implementations, the tensioning spring can be sized and biased such that the distal tip of the inner cannula can contact the inner distal wall of the outer cannula. This may limit any lateral or undesired movement generated due to whip at the distal end of the inner cannula caused by the rotation of the flexible torque coil.

In some implementations, the endoscopic instrument also includes a lavage connector including an irrigation entry port and a tubular member coupled to the lavage connector and the flexible outer tubing. An inner wall of the tubular member and the outer wall of the flexible torque coil can define a second portion of the irrigation channel that is fluidly coupled to the first portion of the irrigation channel. In some implementations, the endoscopic instrument also includes a rotational coupler coupling the flexible outer tubing to the tubular member and configured to cause the flexible outer tubing to rotate relative to the tubular member and cause the opening defined in the outer cannula to rotate relative to the inner cannula. In some implementations, the lavage connector defines an inner bore within which the flexible torque coil is disposed.

In some implementations, the endoscopic instrument also includes a lining within which the flexible torque coil is disposed, the outer wall of the lining configured to define a portion of the irrigation channel. In some implementations, the inner cannula is configured to rotate about a longitudinal axis of the inner cannula and relative to the outer cannula and the aspiration channel is configured to provide a suction force at the opening of the inner cannula.

In some implementations, the flexible torque coil includes a plurality of threads. Each of the plurality of threads can be wound in a direction opposite to a direction in which one or more adjacent threads of the plurality of threads is wound. In some implementations, the flexible torque coil includes a plurality of layers. Each of the plurality of layers can be wound in a direction opposite to a direction in which one or more adjacent layers of the plurality of layers is wound. In some implementations, each layer can include one or more threads. Additional details regarding the flexible torque coil are described above in regard to the discussion of the flexible cable with respect to at least FIGS. 22A-22H.

In some implementations, the flexible outer tubing has a length that exceeds the length of the endoscope in which the endoscopic instrument is insertable. In some implementations, the flexible outer tubing has a length that is at least 100 times larger than an outer diameter of the flexible outer tubing. In some implementations, the flexible portion is at least 40 times as long as the cutting assembly.

FIGS. 40A-40B show a perspective view of an endoscopic tool 4000 and a portion of a drive assembly 4050 configured to drive the endoscopic tool. FIG. 40B shows a perspective view of the endoscopic tool and the portion of the drive assembly configured to drive the endoscopic tool shown in FIGS. 40A-40B. Referring now also to FIGS. 41, 42 and 43, FIG. 41 shows a top view of the endoscopic tool 4000 and a top exposed view of the portion of the drive assembly 4050 shown in FIGS. 40A-40B. FIG. 42 shows a cross-sectional view of the endoscopic tool 4000 and the portion of the drive assembly 4050 across the section A-A. FIG. 43 shows an enlarged1 view of the drive connector of the endoscope and the portion of the drive assembly 4050. FIG. 44 shows a perspective view of the endoscopic tool 4000 and a portion of the drive assembly shown in FIGS. 40A-40B. FIG. 45 shows a cross-sectional view of the endoscopic tool and the portion of the drive assembly across the section B-B. FIG. 46 shows an enlarged cross-sectional view of the rotational coupler section of the endoscopic tool. FIG. 47A and FIG. 47B show a top view and a cross-sectional view of the rotational coupler of the endoscopic tool.

The endoscopic tool 4000, as shown in FIGS. 40A-47B, may be configured to be inserted within an instrument channel of an endoscope. Examples of the endoscope can include a gastroscope, such as a colonoscope, a laryngoscope, or any other flexible endoscope. The endoscopic tool can include a flexible portion 4002 that is shaped, sized and configured to be inserted within the instrument channel, while a remaining portion of the endoscopic tool 4000 can be configured to remain outside the instrument channel of the endoscope. The flexile portion 4002 can be shaped and sized to fit within the instrument channel and be configured to navigate through a tortuous path defined by the instrument channel while the endoscope is inserted within the patient. In the case of colonoscopes, the endoscope can form a series of bends of over at least 60 degrees and in some situations, over 90 degrees.

The endoscopic tool 4000 can include a cutting assembly 4010 configured to resect material at a site within a subject. The cutting assembly 4010 can be similar to the cutting assembly 160 described in FIG. 1C and elsewhere in the description and figures. In some implementations, the cutting assembly 4010 can include an outer cannula and an inner cannula disposed within the outer cannula. The outer cannula can define an opening 4012 through which material to be resected can enter the cutting assembly 4010. In some implementations, the opening 4012 is defines through a portion of the radial wall of the outer cannula. In some implementations, the opening may extend around only a portion of the radius of the outer cannula, for example, up to one third of the circumference of the radial wall. As the aspiration channel 4090 extends between the aspiration port 4092 and the opening 4012, any suction applied at the aspiration port 4092 causes a suction force to be exerted at the opening 4012. The suction force causes material to be introduced into the opening of the outer cannula, which can then be cut by the inner cannula of the cutting assembly.

The inner cannula can include a cutting section that is configured to be positioned adjacent to the opening 4012 such that material to be resected that enters the cutting assembly via the opening 4012 can be resected by the cutting section of the inner cannula. The inner cannula may be hollow and an inner wall of the inner cannula may define a portion of an aspiration channel that may extend through the length of the endoscopic tool. A distal end of the inner cannula can include the cutting section while a proximal end of the inner cannula can be open such that material entering the distal end of the inner cannula via the cutting section can pass through the proximal end of the inner cannula. In some implementations, the distal end of the inner cannula can come into contact with an inner surface of a distal end of the outer cannula. In some implementations, this can allow the inner cannula to rotate relative to the outer cannula along a generally longitudinal axis, providing more stability to the inner cannula while the inner cannula is rotating. In some implementations, the size of the opening can dictate the size of the materials being cut or resected by the inner cannula. As such, the size of the opening may be determined based in part on the size of the aspiration channel defined by the inner circumference of the flexible torque coil.

The endoscopic instrument 4000 can include a flexible torque coil 4080 that is configured to couple to the proximal end of the inner cannula at a distal end of the flexible torque coil 4080. The flexible torque coil can include a fine coil with multiple threads and multiple layers, which can transmit the rotation of one end of the flexible torque coil to an opposite end of the flexible torque coil. Each of the layer of thread of the flexible torque coil can be wound in a direction opposite to a direction in which each of the layer of thread adjacent to the layer of thread is wound. In some implementations, the flexible torque coil can include a first layer of thread wound in a clockwise direction, a second layer of thread wound in a counter-clockwise direction and a third layer of thread wound in a clockwise direction. In some implementations, the first layer of thread is separated from the third layer of thread by the second layer of thread. In some implementations, each of the layers of thread can include one or more threads. In some implementations, the layers of thread can be made from different materials or have different characteristics, such as thickness, length, among others.

The flexibility of the torque coil 4080 allows the coil to maintain performance even in sections of the torque coil 4080 that are bent. Examples of the flexible torque coil 4080 include torque coils made by ASAHI INTECC USA, INC located in Santa Ana, Calif., USA. In some implementations, the flexible torque coil 4080 can be surrounded by a sheath or lining to avoid frictional contact between the outer surface of the flexible torque coil 4080 and other surfaces. In some implementations, the flexible torque coil 4080 can be coated with Polytetrafluoroethylene (PFTE) to reduce frictional contact between the outer surface of the flexible torque coil 4080 and other surfaces. The flexible torque coil 4080 can be sized, shaped or configured to have an outer diameter that is smaller than the diameter of the instrument channel of the endoscope in which the endoscopic tool is to be inserted. For example, in some implementations, the outer diameter of the flexible torque coil can be within the range of 1-4 millimeters. The length of the flexible torque coil can be sized to exceed the length of the endoscope. In some implementations, the inner wall of the flexible torque coil 4080 can be configured to define another portion of the aspiration channel that is fluidly coupled to the portion of the aspiration channel defined by the inner wall of the inner cannula of the cutting assembly 4010. A proximal end of the flexible torque coil 4080 can be coupled to a proximal connector assembly 4070, details of which are provided below.

The endoscopic instrument 4000 can include a flexible outer tubing 4086 that can be coupled to the proximal end of the outer cannula. In some implementations, a distal end of the flexible outer tubing 4086 can be coupled to the proximal end of the outer cannula using a coupling component. In some implementations, the outer cannula can be configured to rotate responsive to rotating the flexible outer tubing. In some implementations, the flexible outer tubing 4086 can be a hollow, braided tubing that has an outer diameter that is smaller than the instrument channel of the endoscope in which the endoscopic instrument 4000 is to be inserted. In some implementations, the length of the flexible outer tubing 4086 can be sized to exceed the length of the endoscope. The flexible outer tubing 4086 can define a bore through which a portion of the flexible outer tubing 4086 extends. The flexible outer tubing 4086 can include braids, threads, or other features that facilitate the rotation of the flexible outer tubing 4086 relative to the flexible torque coil, which is partially disposed within the flexible outer tubing 4086.

The endoscopic instrument 4000 can include a rotational coupler 4030 configured to be coupled to a proximal end of the flexible outer tubing 4086. The rotational coupler 4030 may be configured to allow an operator of the endoscopic tool to rotate the flexible outer tubing 4086 via a rotational tab 4032 coupled to or being an integral part of the rotational coupler 4030. By rotating the rotational tab 4032, the operator can rotate the flexible outer tubing and the outer cannula along a longitudinal axis of the endoscope and relative to the endoscope and the inner cannula of the cutting assembly 4010. In some implementations, the operator may want to rotate the outer cannula while the endoscopic instrument is inserted within the endoscope while the endoscope is within the patient. The operator may desire to rotate the outer cannula to position the opening of the outer cannula to a position where the portion of the radial wall of the outer cannula within which the opening is defined may aligned with the camera of the endoscope such that the operator can view the material entering the endoscopic instrument for resection via the opening. This is possible in part because the opening is defined along a radial wall extending on a side of the outer cannula as opposed to an opening formed on the axial wall of the outer cannula.

In some implementations, a proximal end 4034 of the rotational coupler 4030 can be coupled to a lavage connector 4040. In some implementations, the rotational coupler 4030 can be a rotating luer component that allows a distal end 4036 of the rotational coupler 4030 rotate relative to the proximal end 4034 of the rotational coupler 4030. In this way, when the flexible outer tubing 4086 is rotated, the component to which the proximal end of the rotational coupler 4030 is coupled, is not caused to rotate. In some implementations, the proximal end 4034 of the rotational coupler 4030 can be coupled to an outer tubular member 4044 configured to couple the proximal end 4034 of the rotational coupler 4030 to the lavage connector 4040. The rotational coupler 4030 can define a bore along a central portion of the rotational coupler 4030 through which a portion of the flexible torque coil 4080 extends. In some implementations, the rotational coupler 4030 can be a male to male rotating luer connector. In some implementations, the rotational coupler can be configured to handle pressures up to 1200 psi.

The lavage connector 4040 can be configured to introduce irrigation fluid into the endoscopic tool 4000. The lavage connector 4040 includes a lavage port 4042 configured to engage with an irrigation source, such as a water container. In some implementations, the lavage connector 4040 can be a Y port used in fluid delivery systems that complies with medical device industry standards and is sized to couple to the flexible outer tubing 4086 or the outer tubular member 4044 that serves to couple a distal end 4048 of the lavage connector 4040 to the proximal end 4034 of the rotational coupler 4030. In some implementations, the lavage connector can define a hollow channel between the proximal end 4046 and the distal end 4048 of the lavage connector 4040 that is sized to allow the flexible torque coil 4080 to pass through the hollow channel defined through the lavage connector 4040.

As described above, the proximal connector assembly 4070 is configured to be coupled to a proximal end of the flexible torque coil 4080. The proximal connector assembly 4070 can be configured to engage with the drive assembly 4050 that is configured to provide torque to the inner cannula via the proximal connector assembly 4070 and the flexible torque coil 4080. The proximal connector assembly 4070 can further define a portion of the aspiration channel and be configured to fluidly couple the aspiration channel to a vacuum source to facilitate the removal of material entering the aspiration channel. In some implementations, a proximal end of the proximal connector assembly 4070 can include an aspiration port 4092 through which the material that enters the endoscopic tool 4000 can be withdrawn from the endoscopic tool 4000.

In some implementations, the endoscopic tool 4000 can be configured to be driven by the drive assembly 4050. The drive assembly 4050 is configured to provide rotational energy from an energy source to the endoscopic tool 4000. The drive assembly 4050 can include a housing 4060 that may house a first beveled gear 4054 and a second beveled gear 4056 that are positioned such that the rotation of the first beveled gear 4054 causes a rotation of the second beveled gear 4056. The second beveled gear 4056 can be coupled to a drive receptacle that is sized and shaped to receive and engage with the proximal connector assembly 4070 of the endoscopic tool 4000. In some implementations, the first beveled gear 4054 can be coupled to a motor (not shown) or other rotational source via a rotational input shaft 4052.

The proximal connector assembly 4070 can include a hollow drive shaft 4072, a coupler 4076 through which the hollow drive shaft 4072 passes and a tensioning spring 4074 coupled to the hollow drive shaft 4072. A distal end of the drive shaft 4072 can be coupled to the proximal end of the flexible torque coil 4080. In some implementations, the drive shaft 4072 and the flexible torque coil 4080 can be permanently coupled to one another. In some implementations, the drive shaft 4072 and flexible torque coil 4080 can be coupled using a coupler, a press fit, a weld, such as a butt weld, or any other attachment means that allows the flexible torque coil 4080 to rotate when the drive shaft 4072 rotates and to allow material passing through the flexible torque coil 4080 to flow through the drive shaft 4072. A proximal end of the drive shaft 4072 can define the aspiration port 4092. In some implementations, the aspiration port 4092 can be configured to engage with a vacuum source causing material entering the opening 4012 to flow through the aspiration channel 4090 and out of the endoscopic tool through the aspiration port 4092.

A coupler 4076, such as a hex-shaped coupler, can be configured to couple with the hollow drive shaft. In some implementations, the hex-shaped coupler is a part of the hollow drive shaft. The coupler 4076 can include an outer wall that is configured to engage with an inner wall of a drive receptacle 4058. The drive receptacle 4058 is coupled to the second beveled gear 4056 and is configured to rotate when the second beveled gear 4056 rotates. In some implementations, the drive receptacle 4058 can be a hollow cylindrical tube. In some implementations, a proximal end 4059 of the drive receptacle 4058 can include an opening defined by an inner wall of the proximal end of the drive receptacle 4058 that has a diameter that smaller than the inner diameter of the remaining portion of the drive receptacle 4058. In some implementations, the diameter of the opening through the proximal end 4059 of the drive receptacle 4058 can be large enough to receive the drift shaft 4072 but small enough to prevent the tensioning spring 4074 coupled to the drive shaft 4072 from passing through the opening. In some implementations, the inner diameter of the remaining portion of the drive receptacle is sized to engage with the coupler 4076.

The tensioning spring 4074 can be biased in such a way that, during operation of the endoscopic tool 4000, the tensioning spring 4074 may prevent the drive shaft 4072, the flexible torque coil 4080 and the inner cannula from sliding towards the proximal end of the endoscopic tool 4000. In some implementations, without the tensioning spring 4074, the inner cannula may slide away from the distal end of the endoscopic tool 4000. This may be due to a force applied by the material to be resected at the opening 4012. In some implementations, the tensioning spring 4074 provides a countering force that prevents the inner cannula from sliding away from the distal end when the inner cannula comes into contact with the material to be resected at the opening 4012. In some implementations, the tensioning spring 4074 can be configured to bias the distal end of the inner cannula to contact an inner wall of the distal end of the outer cannula. In some implementations, the tensioning spring 4074 can be sized and biased such that the distal tip of the inner cannula can contact the inner distal wall of the outer cannula. This may limit any lateral or undesired movement generated due to whip at the distal end of the inner cannula caused by the rotation of the flexible torque coil.

The housing 4060 can be configured to engage with an aspiration end cap 4062 and a locking collar 4064. In some implementations, the aspiration end cap 4062 can be configured to allow a vacuum source to maintain a secure connection with the aspiration port 4092 of the drive shaft 4072. In some implementations, the aspiration end cap 4062 can be configured to allow the drive shaft 4072 to rotate while maintaining a secure connection between the vacuum source and the aspiration port 4092 of the drive shaft 4072. In some implementations, the aspiration end cap 4062 can be configured to be secured to a portion of the housing 4060 in such a way that the aspiration port of the drive shaft 4072 is accessible via an opening of the aspiration end cap 4062. In some implementations, the vacuum source can be coupled to the end cap 4062 such that the vacuum source does not rotate along with the proximal end of the drive shaft 4072. In some implementations, one or more bearings or bushings can be used to allow facilitate a fluid connection between the aspiration port 4092 of the drive shaft 4072 and the vacuum source without causing the vacuum source to rotate with the drive shaft 4072.

The locking collar 4064 can be configured to secure the lavage connector 4040 to the proximal connector assembly 4070. In some implementations, the locking collar 4064 can be configured to secure a proximal end 4046 of the lavage connector 4040 to the housing 4060 of the drive assembly 4050. The locking collar 4064 can further be configured to prevent the proximal connector assembly 4070 from disengaging with the drive receptacle 4058 and moving towards the distal end of the endoscopic tool 4000. In some implementations, the locking collar 4064 can be configured to secure a lining 4082 within which the flexible torque coil 4080 is disposed to the flexible torque coil 4080, the drive shaft 4072 or the housing 4060. In some implementations, the lining 4082 can serve as a heat shrink to reduce the dissipation of heat generated in the flexible torque coil to other components of the endoscopic tool. In some implementations, the outer wall of the lining 4082 can define a portion of the irrigation channel, while the inner wall of the lining 4082 can serve to prevent any material passing through the aspiration channel from escaping through the walls of the flexible torque coil. In some implementations, the lining 4082 can also prevent the irrigation fluid passing through the irrigation channel to flow into the aspiration channel 4090 through the walls of the flexible torque coil 4080.

The distal end 4048 of the lavage connector 4040 can be configured to engage with an inner wall of the outer tubing 4044. In some implementations, the distal end 4048 of the lavage connector 4040 can be press fit into a proximal end of the outer tubing 4044. In some implementations, a connector connecting the distal end 4048 of the lavage connector 4040 and the outer tubing can be used. The inner wall of the outer tubing 4044 and the outer wall of the lining 4082 can define a portion of the irrigation channel 4096. The outer tubing 4044 can extend from the distal end 4048 of the lavage connector 4040 to a proximal end 4034 of the rotational coupler 4030. The distal end of the outer tubing 4044 can be configured to engage with the proximal end 4034 of the rotational coupler 4030.

In some implementations, the irrigation channel can extend from the irrigation entry port to the opening of the outer cannula. The irrigation channel can be defined by the inner wall of the outer tubular member, the rotational coupler, the inner wall of the outer tubing and the inner wall of outer cannula. In some implementations, the irrigation channel can also be defined by the outer wall of the inner cannula and the outer wall of the flexible torque coil 4080. In some implementations, the endoscopic instrument 4000 can also include the hollow lining 4082 that is sized to fit around the flexible torque coil 4080. In some implementations, the hollow lining 4082 can serve as a barrier between the irrigation channel 4096 and the aspiration channel 4090. In some implementations, the hollow lining 4082 can prevent air or other fluids to seep through the threads of the flexible torque coil 4080. In addition, the hollow lining can allow the aspiration channel to maintain a suction force throughout the length of the aspiration channel by preventing air to escape or enter through the threads of the flexible torque coil 4080.

As described above, the cutting assembly 4010 includes the outer cannula. The braided tubing 4086 is coupled to the outer cannula such that rotating the rotational tab 4032 of the rotational coupler 4030 results in rotating the outer cannula. The outer cannula includes the opening 4012 at a distal end of the outer cannula. The opening is defined within a portion of the radial wall of the outer cannula and may only extend around a portion of the radius of the outer cannula. As the aspiration channel 4090 extends between the aspiration port 4092 and the opening 4012, any suction applied at the aspiration port 4092 causes a suction force to be exerted at the opening 4012. The suction force causes material to be introduced into the opening of the outer cannula, which can then be cut by the inner cannula of the cutting assembly. In some implementations, the aspirated material can be collected in a collection cartridge. In some implementations, the collection cartridge can be fluidly coupled to the proximal end of the aspiration channel.

The inner cannula is disposed within the outer cannula and configured to resect any material that is sucked into or otherwise enters the opening 4012 due to the suction force in the aspiration channel 4090. The inner cannula can cut, resect, excise, debride or shave the material at the opening 4012 based in part on the interaction between the cutting surface and the wall of the outer cannula that defines the opening. In some implementations, the rotational movement of the cutting surface relative to the opening 4012 can cause the material to be cut, resected, excised, or shaved. The flexible torque coil is coupled to the inner cannula and causes the inner cannula to rotate along the longitudinal axis of the inner cannula. As the outer cannula is coupled to the outer tubing and is not rotationally coupled to the inner cannula or flexible torque coil, the inner cannula rotates relative to the outer cannula. A gap between an outer wall of the inner cannula and the inner wall of the outer cannula defines a portion of the irrigation channel through which irrigation fluid can flow from the lavage connector 4040 through the irrigation channel portion defined in part by the outer tubing 4044, the rotational coupler 4030, and the flexible outer tubing 4086 towards the cutting surface of the inner cannula. The inner cannula may define a portion of the aspiration channel through which excised or resected material and the irrigation fluid can flow from the cutting surface of the inner cannula towards the aspiration port 4092.

The length of the cutting assembly 4010 may be sized to allow the endoscopic instrument 4000 to traverse through the length of the endoscope while the endoscope is inserted inside a patient. In some implementations, the endoscope may be disposed within the patient and the endoscope may include bends that exceed 60 degrees. As such, the length of the cutting assembly 4010 may not exceed a few centimeters. In some implementations, the length of the cutting assembly 4010 may be less than 1% of the length of the endoscopic tool 4000, or the length of the flexible portion of the endoscope within which the endoscopic tool can be inserted. As described above, tissue sensing capabilities can be implemented with the cutting assembly serving as a portion of the tissue sensor.

It should be appreciated that one or more seals, bearings, and other components may be used. Seals may be used to maintain pressure, prevent fluid leaks, or to securely engage components to one another. In some implementations, bearings may be used to allow components to rotate relative to one another without adversely affecting the components or the performance of the endoscopic tool.

FIG. 45 shows a cross-sectional view of the endoscopic tool and the portion of the drive assembly across the section B-B. As shown in FIG. 45, the second beveled gear 4056 may be configured to engage with the drive receptacle 4058 of the drive assembly 4050. The proximal connector 4070 of the endoscopic tool 4000, which includes the coupler 4076 and the drive shaft 4072, can be inserted disposed within the drive receptacle 4058. The outer wall of the coupler 4076 is sized to engage with the inner wall of the drive receptacle 4058 such that when the drive receptacle 4058 rotates, the coupler 4076 also rotates. Because the coupler 4076 is coupled to the drive shaft 4072, the drive shaft 4072 may also rotate when the drive receptacle 4058 rotates. The inner wall of the drive shaft defines a portion of the aspiration channel 4090.

FIG. 46 shows an enlarged cross-sectional view of the rotational coupler section of the endoscopic tool. FIG. 47A and FIG. 47B show a top view and a cross-sectional view of the rotational coupler of the endoscopic tool.

As shown in FIGS. 46-47B, the outer tubing 4044 is configured to engage with the rotational coupler 4030. The outer tubing 4044 surrounds the lining 4082, which in turn surrounds the flexible torque coil 4080. The inner wall of the flexible torque coil 4080 may define a portion of the aspiration channel 4090. The space between the inner wall of the outer tubing 4044 and the outer wall or surface of the lining 4082 defines a portion of the irrigation channel. The tab 4032 can be configured to be rotated by an operator of the endoscopic tool. In some implementations, the operator can rotate the tab 4032 while the endoscopic tool is inserted within the instrument channel of the endoscope and cause the outer cannula to rotate relative to the inner cannula and the endoscope. In this way, the operator can position the opening defined through the outer cannula by rotating the outer cannula to a desired position. In some implementations, by providing a mechanism through which the outer cannula can be rotated relative to the endoscope, an operator does not have to be concerned about the position of the opening when the endoscopic tool is inserted within the instrument channel of the endoscope as the operator may be able to adjust the position of the opening by causing the outer cannula to rotate while the endoscopic tool is inserted within the endoscope.

FIG. 48 is a perspective view of a portion of the endoscopic tool inserted for operation within a drive assembly. The drive assembly 4800 includes a drive interface 4810 configured to receive the proximal connector 4070 of the endoscopic tool 4000. The proximal connector 4070 can engage with the drive receptacle of the drive interface 4810 to translate rotational energy generated by the drive assembly 4800 to the cutting assembly of the endoscopic tool 4000. The drive assembly 4800 may include a pump 4820 or other fluid displacement device to control the flow of irrigation fluid into the lavage port 4042 of the endoscopic tool 4000. In some implementations, the pump 4820 can be a peristaltic pump. In some implementations, the pump can be any positive displacement fluid pump. In some implementations, a valve between the pump 4820 and the lavage port 4042 can be placed to control an amount of irrigation fluid entering the endoscopic tool. In some implementations, the speed at which the pump 4820 operates can dictate the rate at which irrigation fluid enters the endoscopic tool. The drive assembly can also include a pinch valve 4830. In some implementations, the pinch valve can be configured to control the application of a suction force applied to the aspiration channel.

In some implementations, an actuator, such as a control switch can be used to actuate the drive assembly 4800. In some implementations, the actuator can be a foot pedal, a hand switch, or any other actuation means for controlling the drive assembly 4800. In some implementations, the actuator can be coupled to the drive means, such as the pump 4820 such that when the actuator is actuated, the pump 4820 begins to rotate, generating torque, which is translated to the proximal connector of the endoscopic tool via the drive interface 4810. The torque applied to the proximal connector can be translated via the flexible torque coil to the inner cannula, thereby causing the inner cannula to rotate relative to the outer cannula. In some implementations, the actuator can be coupled to a pinch valve, such as the pinch valve 4830 to control the amount of suction applied to the aspiration channel. In some implementations, the actuator can be configured to actuate both the drive means and the pinch valve simultaneously, such that the inner cannula is rotating while suction is applied through the aspiration channel. In some implementations, the actuator can also be coupled to an irrigation control switch or valve that controls the flow of irrigation fluid into the endoscopic tool via the irrigation entry port 4042. In some implementations, the actuator can be configured to actuate the drive means, the pinch valve for aspiration and the irrigation control switch for irrigation simultaneously, such that the inner cannula is rotating while suction is applied through the aspiration channel and irrigation fluid is supplied to the endoscopic tool.

In some implementations, a separate irrigation control switch can be configured to control the flow of irrigation fluid through the irrigation channel of the endoscopic tool. An operator can control the volume of irrigation fluid provided to the irrigation channel via the irrigation control switch.

The drive assembly configuration shown in FIGS. 40A-48 is one example configuration of a drive assembly. It should be appreciated that the endoscopic tool 4000 can be configured to be driven by other drive assembly configurations. In some implementations, the proximal connector portion of the endoscopic tool 4000 can be modified to engage with other drive assembly configurations. In some implementations, the endoscopic tool 400 can be configured to be packaged as one or more different components that can be assembled prior to inserting the endoscopic tool within the instrument channel of the endoscope. In some implementations, the proximal connector of the endoscopic tool 4000 can be assembled together by an operator of the endoscopic tool after one or more components of the endoscopic tool are caused to engage with components of the drive assembly.

FIG. 49 illustrates another implementation of the endoscopic tool and a drive assembly configured to drive the endoscopic tool. FIG. 50A is a side view of the endoscopic tool and drive assembly shown in FIG. 49. FIG. 50B is a cross-sectional view of the endoscopic tool and drive assembly shown in FIG. 49 taken along the section A-A. The endoscopic tool 4910 is similar to the endoscopic tool 4000 but differs from the endoscopic tool 4000 in that the endoscopic tool 4910 has a different proximal connector 4912. In this implementation, the proximal connector 4912 can be coupled to a flexible torque coil, similar to the flexible torque coil 4000 shown in FIGS. 40A-43, and include a proximal connector engagement structure 4914 that is configured to engage with a drive assembly 4950. The proximal connector engagement structure can be sized to engage with the drive assembly 4950 and include one or more engagement surfaces configured to engage with the drive assembly 4950. The engagement surfaces can be coupled to the drive shaft included within the proximal connector 4912 such that when the drive assembly 4950 applies a rotating force to the engagement surfaces, the drive shaft rotates, which in turn causes the flexible torque coil and cutting assembly of the endoscopic tool 4900 to rotate. In some implementations, the engagement surfaces 4914 can be cylindrical objects having an outer wall configured to engage with the drive assembly 4950 and an inner wall configured to engage with an outer wall of the drive shaft. In some implementations, the proximal connector 4910 can also include a fin 4916 or other structure that prevents the proximal connector 4910 and endoscopic tool 4910 from rotating relative to the drive assembly 4950. In some implementations, a side of the fin 4916 can rest on or engage with a mounting structure 4936 a and 4936 b. In this way, when a rotating force is applied by the drive assembly on the engagement surfaces, the fin 4916 prevents the proximal connector 4910 from rotating relative to the drive assembly 4950. The mounting structures 4936 can be configured such that various components of the drive assembly 4950 can be mounted on or receive support from the mounting structures 4936.

The drive assembly 4950 can include a retractable arm 4922, one or more spring loaded bearings 4924, a drive belt 4932 and a drive wheel 4936 and one or more stationary bearings 4940. The retractable arm 4922 can be configured to rotate between a first position and a second position. The spring loaded bearings 4924 can be mounted to the retractable arm 4922 and positioned such that when the retractable arm 4922 is in the first position as shown in FIGS. 49 and 50A-B, the spring loaded bearings 4924 can apply a force on the proximal connector 4912 causing the proximal connector to remain in place while the drive assembly 4950 is actuated. The spring loaded bearings 4924 can be positioned such that when the proximal connector 4912 of the endoscopic tool 4910 is engaged with the drive assembly 4950, the spring loaded bearings 4924 engage with an engagement component 4916 of a drive shaft (not shown) disposed within the proximal connector 4912. The engagement component 4916 can be strategically located on the proximal connector 4912 such that when the retractable arm 4922 is in the first position, the spring loaded bearings 4924 come into contact with the engagement component 4916. The engagement component 4916 can be cylindrical in shape and surround the drive shaft disposed within the proximal connector 4912. The engagement component 4916 can form a portion of the outer wall of the proximal connector 4912. In some implementations, the engagement component 4916 can rotate along a longitudinal axis of the proximal connector 4912 and rotate relative to the proximal connector 4912. In some implementations, the drive wheel 4936 can be an elastomeric friction drive wheel.

A drive means, such as a motor or other driving source, can drive the drive wheel 4936 mounted on a mounting shaft 4930 via the drive belt 4934 that moves when the drive means is actuated. The drive belt 4934 can cause the drive wheel 4936 to rotate. The engagement component 4916 of the proximal connector 4912 can be configured to contact the drive wheel 4936 when the endoscopic tool is positioned within the drive assembly 4950. A stationary bearing 4940 of the drive assembly 4950 can be positioned to hold the proximal connector 4912 in place while the rotation of the drive wheel 4936 causes the engagement component 4916 to rotate. The stationary bearing 4940 can also provide a force causing the drive wheel 4936 and the engagement component 4916 to maintain contact.

As shown in FIG. 50B, when the retractable arm is in the first position, or engaged position, the spring loaded bearings 4924 are in contact with the one or more engagement components 4916 at a first side and the drive wheel 4936 is in contact with the engagement components 4916 at a second side. The spring loaded bearings may allow the engagement components 4916 to rotate when the drive wheel is rotating. The fin 4914 rests against the mounting structures of the drive assembly preventing the endoscopic tool from rotating. When the retractable arm is in a second position, or disengaged position, the spring loaded bearings 4924 are not in contact with the one or more engagement components 4916. As such, the endoscopic tool is not securely positioned within the drive assembly, and as such, actuating the drive means may not cause the flexible torque coil within the endoscopic tool to rotate.

It should be appreciated that the outer diameter of the endoscopic instrument may be sized to be inserted within the instrument channel of an endoscope while the endoscope is inserted within a patient. In addition, the endoscopic instrument may be sized to be large enough that the endoscopic tool comes into contact with the inner walls of the instrument channel at various portions of the instrument channel to maintain stability of the endoscopic instrument. If the outer diameter of the endoscopic instrument is much smaller than the inner diameter of the instrument channel, there may be a large amount of space between the endoscopic instrument and the inner wall of the instrument channel, which may allow the endoscopic instrument to move, vibrate or otherwise experience some instability during operation.

B. Improved Mechanisms for Controlling Outer Cannula for Use in Endoscopic Tool

It should be appreciated that one of the functions of the outer tubing 4086 of the endoscopic tool shown in FIG. 40 is to allow an operator of the endoscopic tool to rotate the outer cannula such that the operator can position a cutting window defined through the outer cannula adjacent to a portion of tissue the operator desires to resect or otherwise remove. The outer tubing, as described above, can be braided such that rotational force applied at a proximal end of the outer tubing can be propagated to the distal end of the outer tubing, which when coupled to the outer cannula, causes rotation of the outer cannula. Due to the length of the outer tubing and the flexibility of the outer tubing, the rotational force applied at the proximal end may not propagate to the distal end of the outer tubing, which gives rise to issues with providing accurate and/or precise control of the position of the cutting window of the outer cannula. Since the outer tubing 4086 also defines a portion of the irrigation path to supply irrigation fluid to the surgical site, the irrigation fluid inside the outer tubing can also interfere with the outer tubing's ability to accurately rotate the outer cannula responsive to a rotational force being applied at the proximal end.

In some implementations, the outer tubing can be a flexible torque coil (referred to as ‘outer flexible torque coil’) similar to the flexible torque coil coupled to the inner cannula. The outer flexible torque coil can be sized similar to the outer tubing 4086 and can have a diameter that is greater than a diameter of the flexible torque coil coupled to the inner cannula. The flexible torque coil can include a sealing component, such as a lining, sleeve or other component that prevents irrigation fluid from seeping or leaking through the outer flexible torque coil. In some implementations, the sealing component can be formed on an inner wall of the flexible torque coil. In some implementations, the sealing component can be formed on an outer wall of the flexible torque coil.

In some implementations, a rotational system can be used to control rotation of the outer cannula from a proximal end of the flexible outer tubing (which remains outside of the subject's body during a procedure). The rotational system can be coupled to, mounted on or included within the flexible outer tubing. In some implementations, the rotational system can include a bearing that is coupled to the outer cannula such that the outer cannula can rotate relative to the flexible outer tubing responsive to an actuation of the rotational system.

In some implementations, the rotational system can include one or more electromagnets positioned proximate to the distal end of the flexible outer tubing. The electromagnets can be positioned at predetermined positions around a radius of the flexible outer tubing and include wires extending through the length of the flexible outer tubing. The electromagnets can be actuated via an electrical current, which upon application of the electrical current, can cause the electromagnet to generate a magnetic field. A ferromagnetic component coupled to the outer cannula can be attracted to the electromagnet responsive to the electrical current being applied, causing the outer cannula to rotate. In some implementations, the electromagnet can generate sufficient attractive forces to cause the outer cannula to remain locked in that position during cutting of tissue. In some implementations, a locking mechanism can be actuated that causes the outer cannula to be locked in place during actuation of the flexible torque coil and the inner cannula such that the outer cannula does not rotate during the procedure. In some implementations, the outer tubing can include a series of magnetic strips with known polarities. The outer cannula, conversely, can be coupled to an electromagnet that depending on how it is actuated, can cause the outer cannula to rotate in a clockwise direction or a counter clockwise direction based on the magnetic polarities of the magnetic strips and the electromagnet.

In some implementations, the rotational system can include a plurality of wires or threads that extend from the proximal end to the distal end of the flexible outer tubing. A first wire can be coupled to a gear or other linear-motion to rotational motion converter such that upon pulling the first wire, could cause the cannula coupled to the gear to rotate in a first direction. Similarly, a second wire can be coupled to another gear or other linear-motion to rotational motion converter such that upon pulling the second wire, the second wire could cause the cannula coupled to the gear to rotate in a second direction opposite the first direction. The amount of linear force applied to the first or second wire can determine an amount the outer cannula can rotate.

In some implementations, the rotational system can include a plurality of gears or motors that are arranged sequentially and physically coupled to adjacent gears or motors and extending from the proximal end to the distal end of the flexible outer tubing. The gears can be embedded in the tubing or formed or otherwise adhered on a radial surface of the flexible outer tubing. The gear at the distal end of the flexible outer tubing can be rotationally coupled to the outer cannula such that a rotational force applied to a first gear at a proximal end can propagate through the plurality of gears sequentially and cause the outer cannula to rotate.

In some implementations, the rotational system can include an electronic control module to control the amount of rotation of the outer cannula. The electronic control module can control an amount of current to the electromagnets and control the timing of the current to provide granular control of the outer cannula. In some implementations, the electronic control module can control an amount of linear force applied to the threads as described in some of the implementations above.

In some implementations, the rotational system can include a motor positioned proximal to the outer cannula towards a distal end of the flexible outer tubing. One or more electrical wires carrying current to the electrical motor can be included in or pass through or within the flexible outer tubing. The electrical motor can be rotationally coupled to the outer cannula and upon receiving an electrical current, can cause the outer cannula to rotate. The length of time for which the motor is actuated can control the amount of rotation of the outer cannula. In some implementations, one or more gears can be used to limit the amount of rotation of the outer cannula from 0 to 360 degrees.

Surgical Instruments with Flexible Outer Tubing for Improved Torque Transmission to End Effector

Referring further to FIG. 40 and now to FIGS. 51-52, in some implementations, a surgical instrument, such as surgical instrument 5100, can be configured to have improved torque transmission using a specialized outer tubing. In various implementations, surgical instruments are used to traverse circuitous, tortuous pathways, such as through the intestine of a subject to reach a site within the subject at which an operation is to be performed by a distal end of the surgical instrument. Various components of the distal end, such as an inner cannula and an outer cannula, are expected to be rotated using torque transmitted to the distal end from an actuator coupled at a proximal end of the surgical instrument (the proximal end may be located outside of the subject). In existing systems, it has been found that there can be non-proportional relationship between the torque applied at the proximal end of the surgical instrument and the resulting rotation of the components of the distal end.

For example, as discussed above, while a braided outer tubing may be used to propagate torque from the actuator to a distal end of the outer tubing in order to rotate the outer cannula, the torque applied at the proximal end may not propagate in proportional manner to the distal end of the outer tubing, which gives rise to issues with providing accurate and/or precise control of the position of the cutting window of the outer cannula. In some implementations, the actuator may be a manual actuator to be rotated by a surgeon or other user performing a surgical procedure using the surgical instrument. To perform the surgical procedure effectively, the user may expect a smooth experience for using the actuator, such that rotating the actuator results in a consistent, proportional rotation response of the outer cannula. However, due to the limitations of existing systems, it has been found that rotating the actuator may result in non-proportional behavior, including but not limited to: a minimum threshold torque needing to be applied in order to cause any rotation of the outer cannula; a significant time delay between torque application and rotation response which is inconsistent with an expected time delay that would be proportional to a length of the outer tubing; a rotation response of the outer cannula that is not proportional to the torque applied by the actuator (e.g., a ratio of (i) the torque applied by the actuator to the outer tubing to (ii) the torque applied by the outer tubing to the outer cannula is not constant as a function of the torque applied by the actuator). These and various other similar behaviors may result in “jerking” or other undesirable rotational movements, limiting the effectiveness of the surgical procedure being performed. It will be appreciated that while these issues are discussed in the context of an surgical instrument, they may similarly arise in any surgical instrument that uses a flexible outer tubing to transmit torque from a proximal end to a distal end in order to rotate a component at the distal end. One possible cause of such inconsistencies in the torque response may arise from the fact that the outer tubing can pass through a tortuous path and include several bends. Also, in some embodiments in which the outer tubing surrounds an inner flexible torque coil, interactions between the outer tubing and the inner flexible torque coil can interfere in the transmission of torque from the proximal end to the distal end.

In some implementations, the relationship between (i) the torque applied by the actuator to the proximal end of the outer tubing (“τ_(proximal)”) to ((ii) the torque applied by the outer tubing to the outer cannula can be represented based on rates of rotation of the torque applied to the outer cannula by the distal end of the outer tubing (“τ_(distal)”). For example, a first rate of rotation associated with the τ_(proximal) can be compared to a second rate of rotation of the outer cannula associated with the τ_(distal) (based on the τ_(proximal)), such as to determine a percentage difference between the first rate of rotation and the second rate of rotation. The rates of rotation may be instantaneous rates or averages rates during a predetermined period of time (e.g., for the first rate of rotation, a first predetermined period of time may be approximately from when rotation of the actuator is initiated to when rotation of the actuator is terminated; for the second rate of rotation, a second predetermined period of time may be approximately from when rotation of the outer cannula in response to rotation of the actuator is initiated to when rotation of the outer cannula is terminated). The rate of rotation may be represented as angle traversed per unit time (e.g., degrees per second or radians per second). In some implementations, a ratio of τ_(proximal) to τ_(distal) may be compared as a function of τ_(proximal), which may indicate whether the rotation response of the outer tubing is linear (or nonlinear) as a function of τ_(proximal). These and other performance characteristics may be correspond to how accurate and/or precise the outer tubing is in rotating a distal component to a desired angular position. For example, with respect to an outer cannula defining a cutting window, it can be desirable to be able to rotate the cutting window to a precise angular position in order to effectively resect material.

Based on various such considerations, it has been identified that a braided outer tubing configured in accordance with the present disclosure (e.g., braided outer tubing 5140 as will be discussed with respect to FIGS. 51-52) can have desirable performance for transmitting torque from an actuator to an outer cannula or other distal component, such as a relatively low percentage difference between τ_(proximal) and τ_(distal), and/or a relatively linear proximal rotation response as a function of τ_(proximal).

Referring further to FIGS. 51-52, a surgical system 5100 including a surgical instrument 5110 is shown. The surgical instrument 5110 can incorporate features of various endoscopic instruments disclosed herein, such as endoscopic tool 4000. As shown in FIG. 51, the surgical instrument 5110 includes a cutting assembly 5120, a flexible outer tubing 5140, and a flexible torque component 5160. The cutting assembly 5120 is configured to resect material at a site within a subject. The cutting assembly 5120 extends from a first proximal end 5122 to a first distal end 5124. The cutting assembly 5120 includes an outer cannula 5126 and an inner cannula 5128 disposed within the outer cannula 5126. The outer cannula defines a cutting window 5130.

The flexible outer tubing 5140 extends from a proximal tubing end 5142 to a distal tubing end 5144. The distal tubing end 5144 is coupled to the outer cannula 5126. The flexible outer tubing 5140 is configured to receive a torque (e.g., τ_(proximal)) at the proximal tubing end 5142 and transmit the torque to the outer cannula (e.g., as τ_(distal)) to rotate the outer cannula.

In some implementations, the surgical system 5100 includes a rotational actuator 5180. The rotational actuator 5180 can be coupled to the proximal tubing end 5142 to rotate the flexible outer tubing 5140. The rotational actuator 5180 can include a manual control input 5182, which can be used to input the τ_(proximal) used to rotate the proximal tubing end 5142 (or to apply a control torque corresponding to a desired τ_(proximal), such as if the rotational actuator 5180 includes gears and/or a motorized actuator to drive the rotation of the proximal tubing end 5142).

The flexible outer tubing 5140 includes a plurality of first wires 5146, and a plurality of second wires 5148 oriented at an angle relative to the plurality of first wires 5146. In some implementations, the plurality of second wires 5148 are oriented such that each second wire 5148 in contact with an adjacent first wire 5146 is substantially perpendicular (e.g., 90 degrees plus or minus 15 degrees; plus or minus 10 degrees; plus or minus 5 degrees) to the adjacent first wire 5146.

In some implementations, the number of the pluralities of wires 5146, 5148 can be selected to improve the performance of the flexible outer tubing 5140 in transmitting torque to the outer cannula 5126. However, there may also be countervailing behaviors that limit the ability to model the performance of the flexible outer tubing 5140 based only on the number of wires (or to improve the performance of the flexible outer tubing 5140 based only on increasing the number of wires). For example, as the number of wires increases, spacing between adjacent wires may decrease, increasing the risk of frictional contact, which may reduce the efficiency of torque transmission to the distal tubing end 5144.

In some implementations, the number of first wires 5146 and the number of second wires 5148 is greater than eight wires and less than or equal to twenty four wires. For example, the number of wires 5146, 5148 may be such that a percentage difference between a rate of rotation of the proximal tubing end 5142 and the distal tubing end 5144 (and/or a percentage difference between an expected rate of rotation of the distal tubing end 5144 and an actual rate of rotation of the distal tubing end 5144, where the expected rate of rotation is consistent with a smooth and/or proportional rotation response as discussed above) may be less than a threshold difference. In some implementations, the threshold difference is less than or equal to thirty percent. In some implementations, the threshold difference is less than or equal to twenty percent. In some implementations, the threshold difference is less than or equal to ten percent. In some implementations, the threshold difference is less than or equal to five percent. In some implementations, a measure of a ratio of τ_(proximal) to τ_(distal) as a function of τ_(proximal) (e.g., over a predetermined range of τ_(proximal) values) can be used to represent the performance of the flexible outer tubing 5140; for example, a ratio of the standard deviation of the ratio to the average value of the ratio can be less than a threshold ratio (which can indicate how constant the ratio of τ_(proximal) to τ_(distal) is as a function of τ_(proximal)). The threshold ratio can be less than or equal to 0.3. The threshold ratio can be less than or equal to 0.2. The threshold ratio can be less than or equal to 0.1. The threshold ratio can be less than or equal to 0.05.

In some implementations, the performance of the flexible outer tubing 5140 may be optimized at a value within the range of greater than eight total wires and less than twenty four total wires. In an example implementation, the performance of the flexible outer tubing 5140 has been determined to be optimized with twelve first wires 5146 and twelve second wires 5148. It will be appreciated that the desires or optimal number of first wires 5146 and second wires 5148 can depend on material properties of the wires 5146, 5148, spacing between wires 5146, 5148, and other properties of the surgical system 5100. The wires 5146, 5148 may be made from stainless steel (e.g., type 304V hard tempered stainless steel).

It should be noted that in a simulation of the performance of the flexible outer tubing 5140, simulated performance values for the flexible outer tubing 5140 were inconsistent with experimental values, and did not identify the optimized performance of the flexible outer tubing 5140 having twelve first wires 5146 and twelve second wires 5148. As such, it may be difficult or impossible to determine the number of wires 5146, 5148 having desired performance based on known principles and, notably, the implementations described herein using greater than eight total wires and less than twenty four total wires, and particularly twelve first wires 5146 and twelve second wires 5148, provided unexpected performance advantages over other implementations.

Referring further to FIG. 52, a cross-section view of the flexible outer tubing 5140 is shown. In some implementations, the flexible outer tubing 5140 includes a base layer 5150 adjacent to the plurality of second wires 5148 and a top layer 5154 adjacent to the plurality of first wires 5146. The base layer 5150 and top layer 5154 may each include at least one of an elastomer or a friction reducing additive. In some implementations, the elastomer includes a thermoplastic elastomer such as polyether block amide (e.g., PEBAX). In some implementations, the friction reducing additive includes MOBILIZE, manufactured by Compounding Solutions, LLC of Lewinston, Me. The at least one of the elastomer or the friction reducing additive can reduce the likelihood of the wires 5146, 5148 sticking to each other, becoming kinked, or otherwise undergoing frictional losses during use that would reduce the efficiency of the flexible outer tubing 5140 in transmitting torque from the proximal tubing end 5142 to the distal tubing end 5144. In addition, the at least one of the elastomer or the friction reducing additive can reduce friction generated between the outer tubing 5140 and the inner flexible torque component 5160 when the outer tubing 5140 and the inner flexible torque component 5160 come in contact with one another, for instance, when the surgical instrument 5100 has been passed through a tortuous pathway. In some embodiments in which the surgical instrument is insertable within a working channel of an endoscope, the at least one of the elastomer or the friction reducing additive can reduce friction generated between the outer tubing 5140 and the inner wall of the working channel of the endoscope.

The flexible outer tubing 5140 defines an inner diameter 5156 and an outer diameter 5158. A ratio of the inner diameter 5156 to the outer diameter 5158 may be greater than or equal to 0.5 and less than or equal to 0.95. The outer diameter 5148 may be less than 0.5 inches. The outer diameter 5148 may be less than 0.25 inches. The outer diameter 5148 may be greater than or equal to 0.05 inches and less than or equal to 0.5 inches. The outer diameter 5148 may be greater than or equal to 0.11 inches and less than or equal to 0.13 inches.

Referring back to FIG. 51, in some implementations, the cutting window 5130 includes a material entry port 5184 through which material to be resected enters the cutting window 5130. The surgical instrument 5110 can include an aspiration channel 5186 extending from the material entry port 5184 to a material exit port 5188. The material exit port 5186 is configured to be coupled to a vacuum source 5190, such that the resected material is received in the aspiration channel 5186 via the material entry port 5184 and removed from the aspiration channel 5186 at the material exit port 5188.

In some implementations, the surgical instrument 5110 includes an irrigation channel 5192. The irrigation channel 5192 extends between the flexible outer tubing 5140 and the flexible torque component 5160, and from a proximal irrigation end 5194 to a distal irrigation end 5196. The irrigation channel 5192 is configured to receive fluid at the proximal irrigation end 5194 from an irrigation source 5198, and output the fluid at the distal irrigation end 5196. As noted above, it will be appreciated that the irrigation fluid inside the flexible outer tubing 5140 can also interfere with the ability of the outer tubing 5140 to accurately rotate the outer cannula 5126 responsive to τ_(proximal) applied at the proximal tubing end 5142.

The flexible torque component 5160 is coupled to a third proximal end 5200 of the inner cannula 5128, so that the flexible torque component 5160 can rotate the inner cannula 5128 relative to the outer cannula 5126. In some implementations, the flexible torque component 5160 is configured to be rotated by a flexible torque drive assembly 5202, which is separate from the rotational actuator 5180.

It should be appreciated that aspects of the disclosure are not limited to an endoscopic tool but rather, extend to other technological areas where there may be a desire to cause rotation of a component at a position where providing a motor or rotational force generator proximate to the component may not be possible or practical. In various surgical instruments similar to surgical instrument 5110, a flexible outer tubing similar or identical to flexible outer tubing 5140 can be used to effectively transmit torque to an end effector. The end effector may be a component which, like outer cannula 5126, is to be driven or rotated as part of a surgical procedure. The end effector may include, without limitation, components such as blades, pincers, scrapers, vacuums, grippers, or electromagnets. In some implementations, a surgical instrument includes an end effector and a flexible outer tubing. The end effector is configured to be rotated by the flexible outer tubing to perform a surgical procedure at a site on or within a subject. The flexible outer tubing extends from a proximal tubing end to a distal tubing end. The distal tubing end is coupled to the end effector so that the flexible outer tubing can receive a torque at the proximal tubing end and transmit the torque to the end effector. The flexible outer tubing includes a plurality of first wires and a plurality of second wires oriented at an angle relative to the plurality of first wires. The plurality of first wires and plurality of second wires each include more than eight wires and less than twenty four wires. The surgical instrument can incorporate (or be part of a system incorporating) various other components described herein, including but not limited to actuators and drive assemblies used to manipulate the surgical instrument, irrigation channels used to deliver fluid via the surgical instrument, and aspiration channels used to remove material from a subject.

It should be appreciated that the Figures shown herein are intended to be for illustrative purposes only and are not intended to limit the scope of the application in any way. In addition, it should be appreciated that the dimensions provided herein are only example dimensions and can vary based on specific requirements. For example, the dimensions may change to alter the aspiration rate, irrigation flow, amount of torque being provided, cutting speed, cutting efficiency, amongst others. Moreover, it should be appreciated that details within the drawings are part of the disclosure. Moreover, it should be appreciated that the shape, materials, sizes, configurations and other details are merely illustrated for the sake of examples and persons having ordinary skill in the art should appreciate that design choices can alter any of the shape, materials, sizes and configurations disclosed herein. For the purpose of this disclosure, the term “coupled” means the joining of two members directly or indirectly to one another. Such joining may be stationary or moveable in nature. Such joining may be achieved with the two members or the two members and any additional intermediate members being integrally formed as a single unitary body with one another or with the two members or the two members and any additional intermediate members being attached to one another. Such joining may be permanent in nature or may be removable or releasable in nature. 

What is claimed is:
 1. A surgical instrument, comprising: a cutting assembly configured to resect material at a site within a subject, the cutting assembly extending from a first proximal end to a first distal end, the cutting assembly comprising an outer cannula and an inner cannula disposed within the outer cannula, the outer cannula defining a cutting window; a flexible outer tubing extending from a proximal tubing end to a distal tubing end, the distal tubing end coupled to the outer cannula, the flexible outer tubing configured to receive a torque at the proximal tubing end and transmit the torque to the outer cannula to rotate the outer cannula, the flexible outer tubing including a plurality of first wires and a plurality of second wires oriented at an angle relative to the plurality of first wires, the plurality of first wires and plurality of second wires each including more than eight wires and less than twenty four wires; and a flexible torque component coupled to a third proximal end of the inner cannula and configured to rotate the inner cannula relative to the outer cannula.
 2. The surgical instrument of claim 1, wherein a number of the plurality of first wires and a number of the plurality of second wires are each selected such that a percentage difference between (1) a rate of rotation associated with the torque received at the proximal tubing end and (2) a rate of rotation of the cutting window based on the torque transmitted to the outer cannula is less than a threshold difference, wherein the threshold difference is less than or equal to thirty percent.
 3. The surgical instrument of claim 2, wherein the threshold difference is less than or equal to ten percent.
 4. The surgical instrument of claim 2, wherein the number of the plurality of first wires and the number of the plurality of second wires are each selected to be twelve wires.
 5. The surgical instrument of claim 2, wherein a spacing between at least two adjacent first wires of the plurality of first wires decreases as the number of wires increases.
 6. The surgical instrument of claim 1, wherein the plurality of second wires are oriented at an angle relative to the plurality of first wires such that each second wire in contact with an adjacent first wire is substantially perpendicular to the adjacent first wire.
 7. The surgical instrument of claim 1, wherein the flexible outer tubing includes a base layer adjacent to the plurality of second wires, the base layer comprising an elastomer and a friction reducing additive, and a top layer adjacent to the plurality of first wires, the top layer comprising the elastomer and the friction reducing additive.
 8. The surgical instrument of claim 1, wherein the cutting window includes a material entry port through which material to be resected enters the cutting assembly, the surgical instrument further comprising an aspiration channel extending from the material entry port to a material exit port configured to be coupled to a vacuum source such that the resected material is received in the aspiration channel via the material entry port and is removed from the aspiration channel at the material exit port.
 9. The surgical instrument of claim 1, further comprising an irrigation channel extending between the flexible outer tubing and the flexible torque component, the irrigation channel configured to receive fluid at a proximal irrigation end and output the fluid at a distal irrigation end, the distal irrigation end adjacent to the outer cannula.
 10. The surgical instrument of claim 1, wherein the plurality of first wires and the plurality of second wires comprise stainless steel.
 11. The surgical instrument of claim 1, wherein the flexible outer tubing is configured to receive the torque from a manual rotational actuator.
 12. The surgical instrument of claim 11, wherein the flexible torque component is configured to be rotated by a drive assembly separate from the manual rotational actuator.
 13. The surgical instrument of claim 1, wherein an outer diameter of the flexible outer tubing is less than 0.5 inches.
 14. The surgical instrument of claim 1, wherein a ratio of an inner diameter of the flexible outer tubing to the outer diameter is greater than or equal to 0.5 and less than or equal to 0.95.
 15. A surgical instrument, comprising: a cutting assembly extending from a first proximal end to a first distal end, the cutting assembly comprising an outer cannula and an inner cannula disposed within the outer cannula, the outer cannula defining a cutting window; a flexible outer tubing extending from a proximal tubing end to a distal tubing end, the distal tubing end coupled to the outer cannula, the flexible outer tubing configured to receive a torque at the proximal tubing end and transmit the torque to the outer cannula to rotate the outer cannula relative to the inner cannula, the flexible outer tubing including a plurality of first wires and a plurality of second wires oriented at an angle relative to the plurality of first wires, the plurality of first wires and plurality of second wires each including twelve wires; and a flexible torque component coupled to a third proximal end of the inner cannula and configured to rotate the inner cannula relative to the outer cannula.
 16. The surgical instrument of claim 15, wherein a percentage difference between (1) a rate of rotation associated with the torque received at the proximal tubing end and (2) a rate of rotation of the cutting window based on the torque transmitted to the outer cannula is less than ten percent.
 17. The surgical instrument of claim 15, wherein the flexible outer tubing includes a base layer adjacent to the plurality of second wires, the base layer comprising an elastomer and a friction reducing additive, and a top layer adjacent to the plurality of first wires, the top layer comprising the elastomer and the friction reducing additive.
 18. The surgical instrument of claim 15, further comprising an irrigation channel extending between the flexible outer tubing and the flexible torque component, the irrigation channel configured to receive fluid at a proximal irrigation end and output the fluid at a distal irrigation end, the distal irrigation end adjacent to the outer cannula.
 19. The surgical instrument of claim 15, wherein the flexible outer tubing is configured to receive the torque from a manual rotatable actuator.
 20. The surgical instrument of claim 15, wherein a ratio of an inner diameter of the flexible outer tubing to an outer diameter of the flexible tubing is greater than or equal to 0.5 and less than or equal to 0.95. 